EP1682039B1 - Prosthesis delivery systems - Google Patents
Prosthesis delivery systems Download PDFInfo
- Publication number
- EP1682039B1 EP1682039B1 EP04782144A EP04782144A EP1682039B1 EP 1682039 B1 EP1682039 B1 EP 1682039B1 EP 04782144 A EP04782144 A EP 04782144A EP 04782144 A EP04782144 A EP 04782144A EP 1682039 B1 EP1682039 B1 EP 1682039B1
- Authority
- EP
- European Patent Office
- Prior art keywords
- prosthesis
- catheter
- outer sheath
- distal end
- releasing means
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Not-in-force
Links
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Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2/07—Stent-grafts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/9517—Instruments specially adapted for placement or removal of stents or stent-grafts handle assemblies therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/954—Instruments specially adapted for placement or removal of stents or stent-grafts for placing stents or stent-grafts in a bifurcation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/962—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve
- A61F2/966—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve with relative longitudinal movement between outer sleeve and prosthesis, e.g. using a push rod
- A61F2/9661—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve with relative longitudinal movement between outer sleeve and prosthesis, e.g. using a push rod the proximal portion of the stent or stent-graft is released first
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2002/065—Y-shaped blood vessels
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2002/9505—Instruments specially adapted for placement or removal of stents or stent-grafts having retaining means other than an outer sleeve, e.g. male-female connector between stent and instrument
- A61F2002/9511—Instruments specially adapted for placement or removal of stents or stent-grafts having retaining means other than an outer sleeve, e.g. male-female connector between stent and instrument the retaining means being filaments or wires
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/962—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve
- A61F2/966—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve with relative longitudinal movement between outer sleeve and prosthesis, e.g. using a push rod
- A61F2002/9665—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve with relative longitudinal movement between outer sleeve and prosthesis, e.g. using a push rod with additional retaining means
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
- A61F2220/0075—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements sutured, ligatured or stitched, retained or tied with a rope, string, thread, wire or cable
Definitions
- the invention relates generally to a prosthesis system for the delivery of a prosthesis to a targeted site within the body, e.g., for the repair of diseased and/or damaged sections of a hollow body organ and/or blood vessel.
- the weakening of a vessel wall from damage or disease can lead to vessel dilatation and the formation of an aneurysm. Left untreated, an aneurysm can grow in size and may eventually rupture.
- aneurysms of the aorta primarily occur in abdominal region, usually in the infrarenal area between the renal arteries and the aortic bifurcation. Aneurysms can also occur in the thoracic region between the aortic arch and renal arteries. The rupture of an aortic aneurysm results in massive hemorrhaging and has a high rate of mortality.
- Open surgical replacement of a diseased or damaged section of vessel can eliminate the risk of vessel rupture.
- the diseased or damaged section of vessel is removed and a prosthetic prosthesis, made either in a straight of bifurcated configuration, is installed and then permanently attached and sealed to the ends of the native vessel by suture.
- the prosthetic prosthesis for these procedures are usually unsupported woven tubes and are typically made from polyester, ePTFE or other suitable materials.
- the prosthesis are longitudinally unsupported so they can accommodate changes in the morphology of the aneurysm and native vessel.
- these procedures require a large surgical incision and have a high rate of morbidity and mortality.
- many patients are unsuitable for this type of major surgery due to other co-morbidities.
- Endovascular aneurysm repair has been introduced to overcome the problems associated with open surgical repair.
- the aneurysm is bridged with a vascular prosthesis, which is placed intraluminally.
- these prosthetic prostheses for aortic aneurysms are delivered collapsed on a catheter through the femoral artery.
- These prostheses are usually designed with a fabric material attached to a metallic scaffolding (stent) structure, which expands or is expanded to contact the internal diameter of the vessel.
- intraluminally deployed prostheses are not sutured to the native vessel, but rely on either barbs extending from the stent, which penetrate into the native vessel during deployment, or the radial expansion force of the stent itself is utilized to hold the prosthesis in position.
- These prosthesis attachment means do not provide the same level of attachment when compared to suture and can damage the native vessel upon deployment.
- WO 98/53761 discloses a self-expanding endovascular prosthesis and an introducer for deploying the prosthesis in a lumen of a patient.
- the introducer has attachment devices for holding each end of the prosthesis and an external sleeve which retains the prosthesis in a compressed condition.
- Another introducer is disclosed in US 6346118 .
- an endovascular prosthesis system according to claim 1.
- Figs. 1A and 1B show a prosthesis delivery catheter 10.
- the purpose of the catheter 10 is to (i) contain and/or restrain a prosthesis 14 prior to its deployment (see Fig. 1B ), (ii) deliver the prosthesis 14 through the vasculature to a desired location within the body, e.g., a hollow body organ or a blood vessel (see Fig. 2 ), and (iii) controllably deploy the prosthesis 14 in the desired location (see Fig. 3 ).
- the prosthesis 14 takes the form of an endovascular, self-expanding stent prosthesis.
- the prosthesis or prostheses 14 may have a wide variety of conventional configurations. It can typically comprise a fabric or some other blood semi-impermeable flexible barrier which is supported by a structure formed by stents 48.
- the stent structure can have any conventional stent configuration, such as zigzag, serpentine, expanding diamond, or combinations thereof.
- the stent structure may extend the entire length of the prosthesis, and in some instances can be longer than the fabric components of the prosthesis. Alternatively, the stent structure can cover only a small portion of the prosthesis, e.g., being present at the ends.
- the stent structure may have three or more ends when it is configured to treat bifurcated vascular regions, such as the treatment of abdominal aortic aneurysms, when the stent prosthesis extends into the iliac arteries.
- the stent structures can be spaced apart along the entire length, or at least a major portion of the entire length, of the stent-prosthesis, where individual stent structures are not connected to each other directly, but rather connected to the fabric or other flexible component of the prosthesis.
- the stent structures could be attached to one another at discrete locations, e.g., in the proximal neck region.
- Such stent structures could comprise individual stents that are connected together when incorporated into the prosthesis, or stents that are manufactured in a joined condition prior to incorporation into the prosthesis.
- the stents 48 may be elastic, e.g., comprised of a shape memory alloy elastic stainless steel, or the like.
- expanding typically comprises releasing the stent structure from a constraint to permit the stent structure to self-expand at the implantation site.
- the catheter 10 places a sheath over the stent structure, in combination with releasable restraining means coupled to the stent structure, to maintain the stent structure in a radially reduced configuration during passage into the body.
- self-expansion of the stent structure is achieved by pulling back on the sheath and release of the restraining means, to permit the stent structure to assume its larger diameter configuration.
- the stent structure may comprise a combination of a self-expanding stent and a malleable stent structure.
- the catheter 10 is shown being positioned over a guidewire 12 in a body lumen.
- the catheter 10 carries the prosthesis 14 in a radially reduced configuration to a targeted site.
- the catheter 10 releases the radially reduced prosthesis 14, which expands radially (see Fig. 3 ).
- one or more fasteners are desirably introduced by a fastener attachment assembly to anchor the prosthesis 14 in place.
- the prosthesis 14 can be sized and configured to be either straight or bifurcated form.
- Fig. 3 depicts a completely deployed straight prosthesis 14.
- Fig. 4 depicts a completely deployed bifurcated prosthesis.
- Fig. 2 shows the targeted site as being within an abdominal aortic aneurysm.
- the targeted site can be elsewhere in the body.
- the catheter 10 comprises an inner assembly 16, an outer sheath 18, and a handle assembly 20. These components will now be individually described in greater detail.
- the inner assembly 16 comprises a central shaft 22, which functions as a carrier for the prosthesis.
- the inner assembly also includes a catheter tip component 24, a releasing means or mechanism 28 for retaining at least a distal portion of the prosthesis 14 in a radially compressed condition prior to deployment, a retaining means or mechanism 26 for maintaining the releasing means 28 in a desired relationship with the central shaft 22 during use, and a spacer 30.
- the central shaft 22, the retaining means 26, the releasing means 28, and the spacer 30 are located within the confines of the outer sheath 18.
- the outer sheath 18 functions as an enclosure for the prosthesis on the carrier.
- the catheter tip component 24 is attached to the distal end of the central shaft 22, and the distal end of the outer sheath 18 terminates adjacent the catheter tip component 24.
- the catheter tip component 24 extends outward beyond the outer sheath 18.
- the central shaft 22, the releasing means 28, and the outer sheath 18 connect to the handle assembly 20 at the proximal end of the catheter 10 (see Fig. 1A ).
- the prosthesis 14 is contained in a cavity 32 defined between the central shaft 22 and the outer sheath 18 in the distal section of the catheter 10 (this arrangement is also shown in Fig. 1B ).
- the central shaft 22 extends from the handle assembly 20 (see Fig. 1A ) to the catheter tip component 24.
- the central shaft 22 may be made, e.g., from stainless steel or other suitable medical materials including other metals or polymers.
- the central shaft 22 desirably has at least one lumen 36 (see Fig. 5A ), with an inner diameter between 0.25 and 3.05 mm (.010 and .120 inches), preferably between 0.76 and 1.52 mm (.03 and .06 inches) and most preferably between 1.02 and 1.27 mm (.04 and .05 inches).
- the central lumen 36 allows for the insertion of a guide wire 12 up to 0.96 mm (0.038") diameter.
- the catheter tip component 24 also desirably has at least one lumen 38 (see Fig. 5A ) configured to align with at least one lumen within the central shaft 22.
- This lumen 38 allows for the insertion of a guide wire 12 through the central shaft 22 and through the catheter tip component 24 (see Fig. 2 ).
- this lumen will have an inner diameter between 0.25 and 3.05 mm (.010 and .120 inches), preferably between 0.76 and 1.52 mm (.03 and .06 inches) and most preferably between 1.02 and 1.27 mm (.04 and .05 inches).
- the catheter tip component 24 is flexible and has a long, tapered distal end and a shorter, tapered proximal end.
- the maximum diameter of the catheter tip component 24 is approximately the same as the outside diameter of the distal end of the outer sheath 18.
- the distal end of the catheter tip component 24 provides a smooth tapered transition from the lumen 38 containing the guide wire 12 to the distal edge of the outer sheath 18. This feature aids in catheter insertion and navigation through tortuous anatomy over the guide wire 12.
- the tapered section on the proximal end of the catheter tip component 24 prevents the catheter tip component 24 from inadvertently engaging the prosthesis 14, portions of the surrounding anatomy, or an introducer sheath or the like during removal of the catheter 10 from the body.
- the retaining means 26 holds the releasing means 28 in a desired, close relationship with the central shaft 22.
- the retaining means 26 orients the releasing means 28 along the axis of the central shaft 22 and allows the releasing means 28 longitudinal movement in this axis.
- the retaining means 26 includes a small hole or recess 40 in the proximal end of the catheter tip component 24 and a tube 56 having a diameter sufficiently large to accommodate both the central shaft 22 and the releasing means 28.
- Figs. 5A , 5B , and 5C the retaining means 26 includes a small hole or recess 40 in the proximal end of the catheter tip component 24 and a tube 56 having a diameter sufficiently large to accommodate both the central shaft 22 and the releasing means 28.
- the tube 56 of the retaining means 26 is located over the central shaft 22 in alignment with and adjacent to the recess 40 on the catheter tip component 24.
- the tube 56 is attached to the central shaft 22 in a manner in that retains a crescent shape lumen 42 between the tube 56 and the central shaft 22.
- the releasing means 28 extends through this lumen 42 and into the recess 40.
- the spacer 30 provides support for the outer sheath 18 and, by occupying space within the outer sheath 18, reduces the amount of air entrapped within the catheter 10.
- the distal end of the spacer 30 desirably terminates adjacent the proximal end of the prosthesis 14 (as Fig. 5B shows).
- the cavity 32 containing the prosthesis 14 extends from the proximal end of the catheter tip component 24 to the distal end of the spacer 30.
- the spacer 30 is positioned over the central shaft 22 and releasing means 28 and the proximal end of the spacer 30 is connected to the handle assembly 20.
- the spacer 30 can have an outer diameter slightly less than the inner diameter of the outer sheath 18.
- the spacer 30 can comprise a single lumen or an array of multiple lumens for passage of the various components within the spacer 30.
- the releasing means 28 holds the prosthesis 14 in a desired configuration prior to deployment (see Fig. 5B ) and selectively releases the prosthesis 14 for deployment (see Fig. 5C ).
- the proximal end of the releasing means 28 is connected to an actuator or control button or knob 46 in the handle assembly 20 (see Fig. 1A ).
- the releasing means 28 extends along the outside of the central shaft 22, through the inside of the spacer 30, and continues distally through the inside of the prosthesis 14.
- the releasing means 28 passes through the prosthesis 14 and the retaining means 26.
- the prosthesis 14 is retained by the releasing means 28 along the central shaft 22 in the cavity 32, which extends between the proximal end of the catheter tip component 24 and the distal end of the spacer 30.
- the releasing means 28 includes a wire 58 that extends along the central shaft 22.
- the distal end of the wire 58 passes through the crescent shape lumen 42 of the retaining means 26, and is ultimately captured in the hole or recess 40 of the retaining means 26 in the proximal end of the catheter tip component 24.
- the distal end of the wire 58 is thereby kept in a desired relationship along the central shaft 22.
- the proximal end of the wire 58 is coupled to the control button 46, such that fore and aft movement of the button 46 advances the wire 58, respectively, distally and proximally.
- the releasing means 28 includes sutures 44 and/or equivalent structures, which are attached to one or more stents 48 on the prosthesis 14.
- the sutures 44 are, in turn, looped around the wire 58 of the releasing means 28, when the wire 58 is in its distal-most position, as Fig. 5B shows.
- Proximal advancement of the wire 58 withdraws the wire 58 from the suture loops 44, as Fig. 5C shows.
- suture loops 44 are shown attached to one or more stents 48 at the distal end of the prosthesis 14. It should be appreciated, however, that suture loops 44 could additionally be attached to stents 44 elsewhere in the prosthesis 14, and/or the other components of the prosthesis 14 as well.
- the suture loops 44 and wire 56 of the embodiment of the releasing means 28 just described retain the prosthesis 14 to the central shaft (see Fig. 5B ).
- the suture loops 44 and the wire 58 keep the prosthesis 14 from moving proximally as the outer sheath 18 is retracted.
- the releasing means 28 also keeps the stents 48 that are coupled to the suture loops 44 in a radially compressed condition as the outer sheath 18 is removed.
- the suture loops 44 and wire 56 prevent the distal end of the prosthesis 14 from self-expanding until the releasing means 28 has been withdrawn.
- the withdrawal of the releasing means 28 is accomplished by operating the control button 46 to move the wire 58 proximally, withdrawing the wire 58 from the hole or recess 40 and away from the suture loops 44. Once the releasing means 28 is withdrawn, the restrained components of the prosthesis 14 are freed to self expand, as Fig. 5C shows.
- the releasing means 28 is coupled to one restrained component of the prosthesis 14. It should be appreciated, however, that the releasing means 28 can be coupled to the prosthesis 14 at two or more restrained regions, so that withdrawal of the releasing means 28 frees the prosthesis at two or more restrained regions. It should also be appreciated that the releasing means 28 can comprise more than a single releasing element. For example, multiple, individual releasing wires 58 could be coupled to the prosthesis 14 at different regions, so that release of separate regions of the prosthesis 14 can be individually controlled.
- the outer sheath 18 also serves to restrain the stents 48 on the prosthesis 14 from expanding and allows for a controlled deployment of the prosthesis 14 within the body.
- the outer sheath 18 is connected to an actuator or a collar or knob 50 on the handle assembly 20.
- the outer sheath 18 extends distally over the spacer 30 and prosthesis 14 and terminates adjacent the proximal end of the catheter tip component 24.
- the outer sheath 18 can be made of a polymer tube and be free of structural reinforcement.
- the outer sheath 18 is tapered due to the difference in outer diameters of the catheter tip component and the spacer 30 (see Fig. 5A ).
- the larger diameter of the outer sheath 18 is intended to contain the main body of the prosthesis 14 and the smaller diameter would contain the leg portion or portions of the prosthesis 14, if present (as in the embodiment shown in Fig. 4 ).
- the smaller diameter continues proximally to the handle assembly 20. This tapered feature of the outer sheath 18 also allows for better blood circulation past the catheter.
- the handle assembly 20 provides the operator with longitudinal and rotational control of the catheter 10 within the body and provides access to the actuator or control means for deploying the prosthesis 14.
- the handle assembly 20 comprises a handle body 52 and the sliding knob or collar 50 which is connected to the proximal and the of the outer sheath 18, and the knob or button 46 which is attached to proximal end of the releasing means 28.
- the central shaft 22 is captured within the handle and has a guide wire receiving luer 34 connected to its proximal end, which is located at the proximal end of the handle assembly 20. This design prevents the position of the prosthesis 14 from moving relative to the handle body 52 while the outer sheath 18 is retracted.
- the sliding knob 50 is moved proximally until the distal end of the outer sheath 18 is free of the prosthesis 14 (see Fig. 8 ).
- the portion or portions of the prosthesis 14 that are not coupled to the releasing means 28 (which, in the illustrated embodiment comprise the proximal region of the prosthesis 14) are free to self-expand, as Fig. 8 shows.
- the portions of the prosthesis 14 that are coupled to the releasing means 58 (which, in the illustrated embodiment comprise only the distal region of the prosthesis 14) are still restrained from self-expansion, despite withdrawal of the outer sheath 18, as Fig. 8 also shows.
- the stent structure of the prosthesis 14 is thereby kept restrained closely against the central shaft tube 22 while the outer sheath 18 is retracted.
- the retaining means 26 prevents the prosthesis 14 from moving relative to the central tube 22 during retraction of the outer sheath 18, which potentially minimizes blood flow through the prosthesis 14 during the deployment process.
- the prosthesis 14 is not "pushed out” of the catheter.
- the prosthesis 14 therefore need not have longitudinal stiffness or a stent structure with a "spine".
- the sliding button 46 is moved proximally until the distal end of the releasing means 28 is withdrawn from the restraining means 26.
- the prosthesis is thereby free to fully self-expand, as Fig. 9 and Fig. 5C show.
- the prosthesis 14 is not released immediately from distal end to proximal end as the sheath 18 is withdrawn.
- the prosthesis 14 is pulled in tension, which "stretches" the prosthesis to its proper length and stent spacing.
- the distal stent or stents 48 are released in a secondary operation, which follows the withdrawal of the outer sheath 18 (as shown in Figs. 5C , 8 , and 9 ).
- Final placement of distal end of the prosthesis 14 can therefore comprise a final step in the deployment process.
- the catheter 10 is navigated over the guide wire 12 to the desired location within the body (as Fig. 2 shows).
- deployment of the prosthesis 14 is achieved in a two step process.
- the outer sheath 18 is retracted and exposes the prosthesis 14 (as Figs. 6 and 7 show).
- the unrestrained portion or portions of the prosthesis 14 self-expand, as Fig. 8 show.
- Figs. 6 and 7 show, during retraction of the outer sheath 18, the prosthesis 14 maintains its position relative to the central shaft 22 due to the releasing means 28 connected to the prosthesis 44.
- the control button or knob 46 on the handle assembly 20 is moved proximally (see Figs. 8 and 9 ). This causes the distal end of the releasing means 28 to be withdrawn and allows the restrained stent or stents 44, and the prosthesis 14 as a whole, to self-expand radially (as Figs. 5C and 9 show).
- the prosthesis 14 enlarges to contact the internal walls of the vessel or hollow body organ, as Fig. 3 shows.
- the catheter 10 can then be withdrawn (as Fig. 10 shows).
- the distal end of a movable component of the releasing means 28 extends along the central shaft 22 in a manner prescribed and controlled by the restraining means 26, i.e., between a tube 56 carried by the central shaft 22 and a recess 40 located in the proximal end of the catheter tip component 24. It is in the region between the tube 56 and the recess 40, that a stationary component of the releasing means 28, which is attached to the prosthesis 14 (e.g., the suture loops 44), is operatively coupled to the movable component of the releasing means 28.
- the restraining means 26 serves to maintain the movable component 58 of the releasing means 28 in a desired operative alignment with the central shaft 22, as well as in a desired operative relationship with the stationary component 44 of the releasing means 28, such that quick and certain release of the prosthesis 14 occurs.
- the releasing means 28 and the restraining means 26 can be variously constructed to meet this objective.
- the distal end of the movable component 58 of the releasing means 28 extends along the central shaft 22 in a manner prescribed and controlled by the restraining means 26, i.e., between adjacent, spaced apart tubes 60A and 60B, without dependence upon additional support by the catheter tip component 24.
- Each tube 60A and 60B surrounds the central shaft 22 in the same fashion as the single tube 56 shown in Figs. 11A to 11C .
- the movable component 58 of the releasing means 28 is held in the region between the two tubes 60A and 60B in operative association with the stationary component 44 of the releasing means 28, and can be quickly and certainly withdrawn from this region to release the prosthesis 14.
- the distal end of the movable component 58 of the releasing means 28 extends along the central shaft 22 between adjacent, spaced apart external tubes 62A and 62B, again without dependence upon additional support by the catheter tip component 24.
- the tubes 62A and 62B project along the exterior of the central shaft 22, but do not surround it.
- a single external support tube like tube 62A or 62B could, alternatively, be used in a hybrid combination with the recess 40 in the catheter tip component 24, if desired.
- the distal end of the movable component 58 of the releasing means 28 extends within a lumen in the central shaft 22, exiting through an aperture 64 in the shaft 22 and into a recess 40 in the catheter tip component 24.
- the movable component 58 of the releasing means 28 is held in the region between the aperture 64 and the recess 40 in operative association with the stationary component 44 of the releasing means 28, and can be quickly and certainly withdrawn from this region to release the prosthesis 14.
- a similar alternative arrangement see Fig.
- the distal end of the movable component 58 of the releasing means 28 extends within a lumen 68 of the central shaft 22 between adjacent, spaced apart apertures 70 and 72.
- the movable component 58 exits the aperture 72 and enters a recess 40 in the catheter tip component 24.
- the movable component 58 of the releasing means 28 is held in the region between the aperture 72 and the recess 40 in operative association with the stationary component 44 of the releasing means 28, and can be quickly and certainly withdrawn from this region to release the prosthesis 14.
- the restraining means 26 includes a single tube 74 carried by the central shaft 22, through which the movable component 58 of the releasing means 28 passes.
- the tube 74 can comprise a surrounding tube of the type shown in Fig. 12A (as Figs. 14A and 14B show) or an external tube of the type shown in Fig. 12B .
- the releasing means 28 includes a suture loop 76 carried by the proximal end of the catheter tip component 24 and a cutting element 78 carried on the distal end of the movable component 58 of the releasing means 28.
- the suture loop 76 passes through the suture loops 44 on the prosthesis 14, as well as through the cutting element 78.
- the cutting element 78 on the distal end of the movable component 58 of the releasing means 28 extends along the central shaft 22 in a manner prescribed and controlled by the restraining means 26, i.e., through and beyond the tube 74, and in operative association with the suture loops 44 and 76, which, in this embodiment, comprise the stationary components of the releasing means 28. This occurs without dependence upon additional support by the catheter tip component 24. withdrawal of the movable component 58 moves the cutting element 78 through the suture loop 76, cutting the suture loop 76 and releasing the prosthesis 14 (as Fig. 14B shows).
- the restraining means 26 includes a single tube 80 carried by the central shaft 22, through which the movable component 58 of the releasing means 28 passes.
- the tube 80 can comprise a surrounding tube of the type shown in Fig. 12A (as Figs. 15A and 15B show) or an external tube of the type shown in Fig. 12B .
- the releasing means 28 includes a wedge element 84 carried on the distal end of the movable component 58 of the releasing means 28.
- the wedge element 84 nests within a mating wedge surface 86 formed in the proximal end of the catheter tip component 24. Advancement of the movable component 58 moves the wedge element 84 into the registration within the wedge surface 86 (as Fig. 15A shows) and out of registration with the wedge surface 86 (as Fig. 15B shows).
- the releasing means 28 in this arrangement further includes alternative embodiments of suture loops 82 or 82', which are pinched between the wedge element 84 and the wedge surface 86 when the element 84 and the surface 86 are in registration, as Fig. 15A shows.
- the embodiment of the suture loop 82 comprises a closed loop 82 carried by a prosthesis stent 48.
- the embodiment of the suture loop 82' comprises an open loop 82' carried by the proximal end of the catheter tip component 24 and looped through a prosthesis stent 48.
- expansion of the prosthesis 14 is restrained (as Fig. 15A shows).
- the wedge element 84 is freed from registration within the wedge surface 86, freeing the loops 82 or 82', thereby releasing the prosthesis 14 for expansion, as Fig. 15B shows.
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Abstract
Description
- The invention relates generally to a prosthesis system for the delivery of a prosthesis to a targeted site within the body, e.g., for the repair of diseased and/or damaged sections of a hollow body organ and/or blood vessel.
- The weakening of a vessel wall from damage or disease can lead to vessel dilatation and the formation of an aneurysm. Left untreated, an aneurysm can grow in size and may eventually rupture.
- For example, aneurysms of the aorta primarily occur in abdominal region, usually in the infrarenal area between the renal arteries and the aortic bifurcation. Aneurysms can also occur in the thoracic region between the aortic arch and renal arteries. The rupture of an aortic aneurysm results in massive hemorrhaging and has a high rate of mortality.
- Open surgical replacement of a diseased or damaged section of vessel can eliminate the risk of vessel rupture. In this procedure, the diseased or damaged section of vessel is removed and a prosthetic prosthesis, made either in a straight of bifurcated configuration, is installed and then permanently attached and sealed to the ends of the native vessel by suture. The prosthetic prosthesis for these procedures are usually unsupported woven tubes and are typically made from polyester, ePTFE or other suitable materials. The prosthesis are longitudinally unsupported so they can accommodate changes in the morphology of the aneurysm and native vessel. However, these procedures require a large surgical incision and have a high rate of morbidity and mortality. In addition, many patients are unsuitable for this type of major surgery due to other co-morbidities.
- Endovascular aneurysm repair has been introduced to overcome the problems associated with open surgical repair. The aneurysm is bridged with a vascular prosthesis, which is placed intraluminally. Typically these prosthetic prostheses for aortic aneurysms are delivered collapsed on a catheter through the femoral artery. These prostheses are usually designed with a fabric material attached to a metallic scaffolding (stent) structure, which expands or is expanded to contact the internal diameter of the vessel. Unlike open surgical aneurysm repair, intraluminally deployed prostheses are not sutured to the native vessel, but rely on either barbs extending from the stent, which penetrate into the native vessel during deployment, or the radial expansion force of the stent itself is utilized to hold the prosthesis in position. These prosthesis attachment means do not provide the same level of attachment when compared to suture and can damage the native vessel upon deployment.
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WO 98/53761 US 6346118 . - According to the present invention there is provided an endovascular prosthesis system according to
claim 1. - Other features and advantages of the invention shall be apparent based upon the accompanying description, drawings, and claims.
- The invention will be understood from the following detailed description of preferred embodiments, taken in conjunction with the accompanying drawings, wherein:
-
Fig. 1A is a perspective view of a prosthesis delivery catheter that embodies features of the invention. -
Fig. 1B is an enlarged perspective view, with portions broken away and in section, of the distal end of the prosthesis delivery catheter shown inFig. 1A . -
Fig. 2 is a perspective view of the prosthesis delivery catheter shown inFig. 1A , being positioned within an abdominal aortic aneurysm. -
Fig. 3 is a perspective view of a straight endovascular prosthesis after deployment by the prosthesis delivery catheter shown inFig. 1A . -
Fig. 4 is a perspective view of a bifurcated endovascular prosthesis after deployment by the prosthesis delivery catheter shown inFig. 1A . -
Fig. 5A is an enlarged perspective view, with portions broken away and in section, of the inner assembly which is located in the distal end of the prosthesis delivery catheter shown inFig. 1A . -
Fig. 5B is an enlarged perspective view, with portions broken away and in section, of the inner assembly which is located in the distal end of the prosthesis delivery catheter shown inFig. 5A , showing a prosthesis retained in a collapsed condition by restraining means prior to deployment. -
Fig. 5C is an enlarged perspective view, with portions broken away and in section, of the inner assembly which is located in the distal end of the prosthesis delivery catheter shown inFig. 5A , showing the prosthesis in an expanded condition after removal of the restraining means. -
Fig. 6 is a side view, with portions broken away and in section, of the prosthesis delivery catheter shown inFig. 1A , showing the catheter retaining a prosthesis in a collapsed condition prior to deployment, the outer sheath being shown in an advanced position over the prosthesis. -
Fig. 7 is a side view, with portions broken away and in section, of the prosthesis delivery catheter shown inFig. 6 , showing the catheter retaining a prosthesis in a collapsed condition prior to deployment, the outer sheath being shown in a position withdrawn from the prosthesis. -
Fig. 8 is a side view, with portions broken away and in section, of the prosthesis delivery catheter shown inFig. 7 , showing the catheter retaining a prosthesis in a collapsed condition prior to deployment, with the pull wire still advanced to restrain radial expansion of the prosthesis. -
Fig. 9 is a side view, with portions broken away and in section, of the prosthesis delivery catheter shown inFig. 8 , showing the prosthesis in a radially expanded condition after actuation of the pull wire to remove the restraining means. -
Fig. 10 is a side view, with portions broken away and in section, of the prosthesis delivery catheter shown inFig. 9 , showing the withdrawal of the catheter from the prosthesis after its deployment. -
Fig. 11A is a simplified side view of the distal end of the prosthesis delivery catheter shown inFig. 5B , with the outer sheath removed, showing the releasing means retaining the prosthesis in a restrained condition. -
Fig. 11B is an end section view of the distal end of the prosthesis delivery catheter shown inFig. 11A , taken generally alongline 11B-11B inFig. 11A . -
Fig. 11C is a simplified side view of the distal end of the prosthesis delivery catheter shown inFig. 5B , with the outer sheath removed, showing an alternative embodiment of a restraining means for maintaining the releasing means in a desired orientation while retaining the prosthesis in a restrained condition. -
Figs. 12A and 12B are simplified side views of the distal end of the prosthesis delivery catheter shown inFig. 5B , with the outer sheath removed, showing other alternative embodiments of a restraining means for maintaining the releasing means in a desired orientation while retaining the prosthesis in a restrained condition, without reliance upon the catheter tip component. -
Figs. 13A and 13B are simplified side views of the distal end of the prosthesis delivery catheter shown inFig. 5B , with the outer sheath removed, showing other alternative embodiments of a restraining means for maintaining the releasing means in a desired orientation while retaining the prosthesis in a restrained condition, without reliance upon a tubular sleeve carried by the central shaft. -
Figs. 14A and 14B are simplified side views of the distal end of the prosthesis delivery catheter shown inFig. 5B , with the outer sheath removed, showing other alternative embodiments of a releasing means with a cutting element for selectively releasing the prosthesis for use, together with an associated restraining means for maintaining the releasing means in a desired orientation for operation. -
Figs. 15A and 15B are simplified side views of the distal end of the prosthesis delivery catheter shown inFig. 5B , with the outer sheath removed, showing other alternative embodiments of a releasing means with a wedge element for selectively releasing the prosthesis for use, together with an associated restraining means for maintaining the releasing means in a desired orientation for operation. -
Figs. 1A and 1B show aprosthesis delivery catheter 10. The purpose of thecatheter 10 is to (i) contain and/or restrain aprosthesis 14 prior to its deployment (seeFig. 1B ), (ii) deliver theprosthesis 14 through the vasculature to a desired location within the body, e.g., a hollow body organ or a blood vessel (seeFig. 2 ), and (iii) controllably deploy theprosthesis 14 in the desired location (seeFig. 3 ). - In the illustrated arrangement (see
Fig. 3 ), theprosthesis 14 takes the form of an endovascular, self-expanding stent prosthesis. In this respect, the prosthesis orprostheses 14 may have a wide variety of conventional configurations. It can typically comprise a fabric or some other blood semi-impermeable flexible barrier which is supported by a structure formed bystents 48. The stent structure can have any conventional stent configuration, such as zigzag, serpentine, expanding diamond, or combinations thereof. The stent structure may extend the entire length of the prosthesis, and in some instances can be longer than the fabric components of the prosthesis. Alternatively, the stent structure can cover only a small portion of the prosthesis, e.g., being present at the ends. The stent structure may have three or more ends when it is configured to treat bifurcated vascular regions, such as the treatment of abdominal aortic aneurysms, when the stent prosthesis extends into the iliac arteries. In certain instances, the stent structures can be spaced apart along the entire length, or at least a major portion of the entire length, of the stent-prosthesis, where individual stent structures are not connected to each other directly, but rather connected to the fabric or other flexible component of the prosthesis. Still, it is contemplated that the stent structures could be attached to one another at discrete locations, e.g., in the proximal neck region. Such stent structures could comprise individual stents that are connected together when incorporated into the prosthesis, or stents that are manufactured in a joined condition prior to incorporation into the prosthesis. - The
stents 48 may be elastic, e.g., comprised of a shape memory alloy elastic stainless steel, or the like. For elastic, expanding typically comprises releasing the stent structure from a constraint to permit the stent structure to self-expand at the implantation site. As will be described in greater detail, thecatheter 10 places a sheath over the stent structure, in combination with releasable restraining means coupled to the stent structure, to maintain the stent structure in a radially reduced configuration during passage into the body. In this arrangement, self-expansion of the stent structure is achieved by pulling back on the sheath and release of the restraining means, to permit the stent structure to assume its larger diameter configuration. - The stent structure may comprise a combination of a self-expanding stent and a malleable stent structure.
- In the illustrated embodiment (see
Fig. 2 ), thecatheter 10 is shown being positioned over aguidewire 12 in a body lumen. Thecatheter 10 carries theprosthesis 14 in a radially reduced configuration to a targeted site. At the targeted site, thecatheter 10 releases the radially reducedprosthesis 14, which expands radially (seeFig. 3 ). After partial or complete expansion or deployment of theprosthesis 14, one or more fasteners are desirably introduced by a fastener attachment assembly to anchor theprosthesis 14 in place. - Further details of the fastener attachment assembly can be found in
US2004/0093057 (United States Patent Application Serial No.10/307,226, filed November 29, 2002 - The
prosthesis 14 can be sized and configured to be either straight or bifurcated form.Fig. 3 depicts a completely deployedstraight prosthesis 14.Fig. 4 depicts a completely deployed bifurcated prosthesis. - For the purposes of illustration,
Fig. 2 shows the targeted site as being within an abdominal aortic aneurysm. Of course, the targeted site can be elsewhere in the body. - As shown in
Figs. 1A and 1B , thecatheter 10 comprises aninner assembly 16, anouter sheath 18, and ahandle assembly 20. These components will now be individually described in greater detail. - In the illustrated embodiment (see
Fig. 5A ), theinner assembly 16 comprises acentral shaft 22, which functions as a carrier for the prosthesis. The inner assembly also includes acatheter tip component 24, a releasing means ormechanism 28 for retaining at least a distal portion of theprosthesis 14 in a radially compressed condition prior to deployment, a retaining means ormechanism 26 for maintaining the releasing means 28 in a desired relationship with thecentral shaft 22 during use, and aspacer 30. - In the embodiment shown in
Fig. 5A , thecentral shaft 22, the retaining means 26, the releasingmeans 28, and thespacer 30 are located within the confines of theouter sheath 18. In this respect, theouter sheath 18 functions as an enclosure for the prosthesis on the carrier. In this arrangement, thecatheter tip component 24 is attached to the distal end of thecentral shaft 22, and the distal end of theouter sheath 18 terminates adjacent thecatheter tip component 24. Thus, thecatheter tip component 24 extends outward beyond the outer sheath 18.Thecentral shaft 22, the releasingmeans 28, and theouter sheath 18 connect to thehandle assembly 20 at the proximal end of the catheter 10 (seeFig. 1A ). In use (seeFig. 5B ), theprosthesis 14 is contained in acavity 32 defined between thecentral shaft 22 and theouter sheath 18 in the distal section of the catheter 10 (this arrangement is also shown inFig. 1B ). - The
central shaft 22 extends from the handle assembly 20 (seeFig. 1A ) to thecatheter tip component 24. Thecentral shaft 22 may be made, e.g., from stainless steel or other suitable medical materials including other metals or polymers. Thecentral shaft 22 desirably has at least one lumen 36 (seeFig. 5A ), with an inner diameter between 0.25 and 3.05 mm (.010 and .120 inches), preferably between 0.76 and 1.52 mm (.03 and .06 inches) and most preferably between 1.02 and 1.27 mm (.04 and .05 inches). - As described, the
central lumen 36 allows for the insertion of aguide wire 12 up to 0.96 mm (0.038") diameter. Thecatheter tip component 24 also desirably has at least one lumen 38 (seeFig. 5A ) configured to align with at least one lumen within thecentral shaft 22. Thislumen 38 allows for the insertion of aguide wire 12 through thecentral shaft 22 and through the catheter tip component 24 (seeFig. 2 ). Typically this lumen will have an inner diameter between 0.25 and 3.05 mm (.010 and .120 inches), preferably between 0.76 and 1.52 mm (.03 and .06 inches) and most preferably between 1.02 and 1.27 mm (.04 and .05 inches). - Preferably, the
catheter tip component 24 is flexible and has a long, tapered distal end and a shorter, tapered proximal end. The maximum diameter of thecatheter tip component 24 is approximately the same as the outside diameter of the distal end of theouter sheath 18. The distal end of thecatheter tip component 24 provides a smooth tapered transition from thelumen 38 containing theguide wire 12 to the distal edge of theouter sheath 18. This feature aids in catheter insertion and navigation through tortuous anatomy over theguide wire 12. The tapered section on the proximal end of thecatheter tip component 24 prevents thecatheter tip component 24 from inadvertently engaging theprosthesis 14, portions of the surrounding anatomy, or an introducer sheath or the like during removal of thecatheter 10 from the body. - Still referring to
Fig. 5A , the retaining means 26 holds the releasing means 28 in a desired, close relationship with thecentral shaft 22. The retaining means 26 orients the releasingmeans 28 along the axis of thecentral shaft 22 and allows the releasing means 28 longitudinal movement in this axis. In the embodiment shown inFigs. 5A ,5B , and5C , the retaining means 26 includes a small hole orrecess 40 in the proximal end of thecatheter tip component 24 and atube 56 having a diameter sufficiently large to accommodate both thecentral shaft 22 and the releasingmeans 28. In the embodiment shown inFigs. 5A ,5B , and5C , thetube 56 of the retaining means 26 is located over thecentral shaft 22 in alignment with and adjacent to therecess 40 on thecatheter tip component 24. Thetube 56 is attached to thecentral shaft 22 in a manner in that retains acrescent shape lumen 42 between thetube 56 and thecentral shaft 22. The releasing means 28 extends through thislumen 42 and into therecess 40. - Returning to
Fig. 5A , thespacer 30 provides support for theouter sheath 18 and, by occupying space within theouter sheath 18, reduces the amount of air entrapped within thecatheter 10. The distal end of thespacer 30 desirably terminates adjacent the proximal end of the prosthesis 14 (asFig. 5B shows). In this arrangement (seeFig. 5B ), thecavity 32 containing theprosthesis 14 extends from the proximal end of thecatheter tip component 24 to the distal end of thespacer 30. AsFig. 5A shows, thespacer 30 is positioned over thecentral shaft 22 and releasingmeans 28 and the proximal end of thespacer 30 is connected to thehandle assembly 20. Typically, thespacer 30 can have an outer diameter slightly less than the inner diameter of theouter sheath 18. Thespacer 30 can comprise a single lumen or an array of multiple lumens for passage of the various components within thespacer 30. - The releasing means 28 holds the
prosthesis 14 in a desired configuration prior to deployment (seeFig. 5B ) and selectively releases theprosthesis 14 for deployment (seeFig. 5C ). In the illustrated embodiment, the proximal end of the releasingmeans 28 is connected to an actuator or control button orknob 46 in the handle assembly 20 (seeFig. 1A ). AsFig. 5B shows, the releasingmeans 28 extends along the outside of thecentral shaft 22, through the inside of thespacer 30, and continues distally through the inside of theprosthesis 14. The releasing means 28 passes through theprosthesis 14 and the retaining means 26. - As
Fig. 5B best shows, theprosthesis 14 is retained by the releasingmeans 28 along thecentral shaft 22 in thecavity 32, which extends between the proximal end of thecatheter tip component 24 and the distal end of thespacer 30. In the illustrated embodiment, the releasingmeans 28 includes awire 58 that extends along thecentral shaft 22. The distal end of thewire 58 passes through thecrescent shape lumen 42 of the retaining means 26, and is ultimately captured in the hole orrecess 40 of the retaining means 26 in the proximal end of thecatheter tip component 24. The distal end of thewire 58 is thereby kept in a desired relationship along thecentral shaft 22. The proximal end of thewire 58 is coupled to thecontrol button 46, such that fore and aft movement of thebutton 46 advances thewire 58, respectively, distally and proximally. - As
Fig. 5B shows (and which is further shown in more schematic form inFigs. 11A, 11B, and 11C ), the releasingmeans 28 includessutures 44 and/or equivalent structures, which are attached to one ormore stents 48 on theprosthesis 14. Thesutures 44 are, in turn, looped around thewire 58 of the releasingmeans 28, when thewire 58 is in its distal-most position, asFig. 5B shows. Proximal advancement of the wire 58 (using the control button 46) withdraws thewire 58 from thesuture loops 44, asFig. 5C shows. - In
Fig. 5B as well asFigs. 11A, 11B, and 11C , thesuture loops 44 are shown attached to one ormore stents 48 at the distal end of theprosthesis 14. It should be appreciated, however, thatsuture loops 44 could additionally be attached tostents 44 elsewhere in theprosthesis 14, and/or the other components of theprosthesis 14 as well. - The
suture loops 44 andwire 56 of the embodiment of the releasing means 28 just described retain theprosthesis 14 to the central shaft (seeFig. 5B ). Thesuture loops 44 and thewire 58 keep theprosthesis 14 from moving proximally as theouter sheath 18 is retracted. The releasing means 28 also keeps thestents 48 that are coupled to thesuture loops 44 in a radially compressed condition as theouter sheath 18 is removed. Thesuture loops 44 andwire 56 prevent the distal end of theprosthesis 14 from self-expanding until the releasingmeans 28 has been withdrawn. In the illustrated embodiment, the withdrawal of the releasingmeans 28 is accomplished by operating thecontrol button 46 to move thewire 58 proximally, withdrawing thewire 58 from the hole orrecess 40 and away from thesuture loops 44. Once the releasingmeans 28 is withdrawn, the restrained components of theprosthesis 14 are freed to self expand, asFig. 5C shows. - As illustrated and described, the releasing
means 28 is coupled to one restrained component of theprosthesis 14. It should be appreciated, however, that the releasingmeans 28 can be coupled to theprosthesis 14 at two or more restrained regions, so that withdrawal of the releasing means 28 frees the prosthesis at two or more restrained regions. It should also be appreciated that the releasingmeans 28 can comprise more than a single releasing element. For example, multiple, individual releasingwires 58 could be coupled to theprosthesis 14 at different regions, so that release of separate regions of theprosthesis 14 can be individually controlled. - The
outer sheath 18 also serves to restrain thestents 48 on theprosthesis 14 from expanding and allows for a controlled deployment of theprosthesis 14 within the body. In the illustrated arrangement, theouter sheath 18 is connected to an actuator or a collar orknob 50 on thehandle assembly 20. AsFig. 5A shows, theouter sheath 18 extends distally over thespacer 30 andprosthesis 14 and terminates adjacent the proximal end of thecatheter tip component 24. Typically, theouter sheath 18 can be made of a polymer tube and be free of structural reinforcement. - The
outer sheath 18 is tapered due to the difference in outer diameters of the catheter tip component and the spacer 30 (seeFig. 5A ). The larger diameter of theouter sheath 18 is intended to contain the main body of theprosthesis 14 and the smaller diameter would contain the leg portion or portions of theprosthesis 14, if present (as in the embodiment shown inFig. 4 ). The smaller diameter continues proximally to thehandle assembly 20. This tapered feature of theouter sheath 18 also allows for better blood circulation past the catheter. - The
handle assembly 20 provides the operator with longitudinal and rotational control of thecatheter 10 within the body and provides access to the actuator or control means for deploying theprosthesis 14. - In the illustrated embodiment, the
handle assembly 20 comprises ahandle body 52 and the sliding knob orcollar 50 which is connected to the proximal and the of theouter sheath 18, and the knob orbutton 46 which is attached to proximal end of the releasingmeans 28. In the illustrated embodiment, thecentral shaft 22 is captured within the handle and has a guidewire receiving luer 34 connected to its proximal end, which is located at the proximal end of thehandle assembly 20. This design prevents the position of theprosthesis 14 from moving relative to thehandle body 52 while theouter sheath 18 is retracted. - To withdraw the
outer sheath 18 from the prosthesis 14 (seeFigs. 6 and7 ), the slidingknob 50 is moved proximally until the distal end of theouter sheath 18 is free of the prosthesis 14 (seeFig. 8 ). The portion or portions of theprosthesis 14 that are not coupled to the releasing means 28 (which, in the illustrated embodiment comprise the proximal region of the prosthesis 14) are free to self-expand, asFig. 8 shows. However, the portions of theprosthesis 14 that are coupled to the releasing means 58 (which, in the illustrated embodiment comprise only the distal region of the prosthesis 14) are still restrained from self-expansion, despite withdrawal of theouter sheath 18, asFig. 8 also shows. The stent structure of theprosthesis 14 is thereby kept restrained closely against thecentral shaft tube 22 while theouter sheath 18 is retracted. The retaining means 26 prevents theprosthesis 14 from moving relative to thecentral tube 22 during retraction of theouter sheath 18, which potentially minimizes blood flow through theprosthesis 14 during the deployment process. Furthermore, as described, theprosthesis 14 is not "pushed out" of the catheter. Theprosthesis 14 therefore need not have longitudinal stiffness or a stent structure with a "spine". - To withdraw the releasing means 28 (see
Figs. 8 and9 ), the slidingbutton 46 is moved proximally until the distal end of the releasingmeans 28 is withdrawn from the restraining means 26. The prosthesis is thereby free to fully self-expand, asFig. 9 andFig. 5C show. As described, theprosthesis 14 is not released immediately from distal end to proximal end as thesheath 18 is withdrawn. As theouter sheath 18 is retracted, theprosthesis 14 is pulled in tension, which "stretches" the prosthesis to its proper length and stent spacing. The distal stent orstents 48 are released in a secondary operation, which follows the withdrawal of the outer sheath 18 (as shown inFigs. 5C ,8 , and9 ). Final placement of distal end of theprosthesis 14 can therefore comprise a final step in the deployment process. - During use, the
catheter 10 is navigated over theguide wire 12 to the desired location within the body (asFig. 2 shows). In the illustrated embodiment, deployment of theprosthesis 14 is achieved in a two step process. First, by pulling the knob orcollar 50 on thehandle assembly 20 proximally, theouter sheath 18 is retracted and exposes the prosthesis 14 (asFigs. 6 and7 show). The unrestrained portion or portions of theprosthesis 14 self-expand, asFig. 8 show. AsFigs. 6 and7 show, during retraction of theouter sheath 18, theprosthesis 14 maintains its position relative to thecentral shaft 22 due to the releasing means 28 connected to theprosthesis 44. - In the second step of the deployment process, following the withdrawal of the
outer sheath 18, the control button orknob 46 on thehandle assembly 20 is moved proximally (seeFigs. 8 and9 ). This causes the distal end of the releasing means 28 to be withdrawn and allows the restrained stent orstents 44, and theprosthesis 14 as a whole, to self-expand radially (asFigs. 5C and9 show). Theprosthesis 14 enlarges to contact the internal walls of the vessel or hollow body organ, asFig. 3 shows. Thecatheter 10 can then be withdrawn (asFig. 10 shows). - In the embodiment shown in
Figs. 11A to 11C (as already described), the distal end of a movable component of the releasing means 28 (e.g., the wire 58) extends along thecentral shaft 22 in a manner prescribed and controlled by the restraining means 26, i.e., between atube 56 carried by thecentral shaft 22 and arecess 40 located in the proximal end of thecatheter tip component 24. It is in the region between thetube 56 and therecess 40, that a stationary component of the releasingmeans 28, which is attached to the prosthesis 14 (e.g., the suture loops 44), is operatively coupled to the movable component of the releasingmeans 28. Movement of themovable component 58 out of this region releases thestationary component 44. The overall objective of the restraining means 26 is achieved: the restraining means 26 serves to maintain themovable component 58 of the releasing means 28 in a desired operative alignment with thecentral shaft 22, as well as in a desired operative relationship with thestationary component 44 of the releasingmeans 28, such that quick and certain release of theprosthesis 14 occurs. - The releasing means 28 and the restraining means 26 can be variously constructed to meet this objective. For example, in the alternative embodiment shown in
Fig. 12A , the distal end of themovable component 58 of the releasingmeans 28 extends along thecentral shaft 22 in a manner prescribed and controlled by the restraining means 26, i.e., between adjacent, spaced aparttubes catheter tip component 24. Eachtube central shaft 22 in the same fashion as thesingle tube 56 shown inFigs. 11A to 11C . Themovable component 58 of the releasingmeans 28 is held in the region between the twotubes stationary component 44 of the releasingmeans 28, and can be quickly and certainly withdrawn from this region to release theprosthesis 14. In a similar alternative arrangement (seeFig. 12B ), the distal end of themovable component 58 of the releasingmeans 28 extends along thecentral shaft 22 between adjacent, spaced apart external tubes 62A and 62B, again without dependence upon additional support by thecatheter tip component 24. InFig. 12B , the tubes 62A and 62B project along the exterior of thecentral shaft 22, but do not surround it. Still, it should be appreciated that a single external support tube like tube 62A or 62B could, alternatively, be used in a hybrid combination with therecess 40 in thecatheter tip component 24, if desired. - In another illustrative, alternative embodiment (see
Fig. 13A ), the distal end of themovable component 58 of the releasingmeans 28 extends within a lumen in thecentral shaft 22, exiting through anaperture 64 in theshaft 22 and into arecess 40 in thecatheter tip component 24. Themovable component 58 of the releasingmeans 28 is held in the region between theaperture 64 and therecess 40 in operative association with thestationary component 44 of the releasingmeans 28, and can be quickly and certainly withdrawn from this region to release theprosthesis 14. In a similar alternative arrangement (seeFig. 13B ), the distal end of themovable component 58 of the releasingmeans 28 extends within alumen 68 of thecentral shaft 22 between adjacent, spaced apart apertures 70 and 72. Themovable component 58 exits theaperture 72 and enters arecess 40 in thecatheter tip component 24. Themovable component 58 of the releasingmeans 28 is held in the region between theaperture 72 and therecess 40 in operative association with thestationary component 44 of the releasingmeans 28, and can be quickly and certainly withdrawn from this region to release theprosthesis 14. - In yet another illustrative, alternative embodiment (see
Figs. 14A and 14B ), the restraining means 26 includes asingle tube 74 carried by thecentral shaft 22, through which themovable component 58 of the releasing means 28 passes. Thetube 74 can comprise a surrounding tube of the type shown inFig. 12A (asFigs. 14A and 14B show) or an external tube of the type shown inFig. 12B . - In this arrangement, the releasing
means 28 includes asuture loop 76 carried by the proximal end of thecatheter tip component 24 and a cutting element 78 carried on the distal end of themovable component 58 of the releasingmeans 28. Thesuture loop 76 passes through thesuture loops 44 on theprosthesis 14, as well as through the cutting element 78. The cutting element 78 on the distal end of themovable component 58 of the releasingmeans 28 extends along thecentral shaft 22 in a manner prescribed and controlled by the restraining means 26, i.e., through and beyond thetube 74, and in operative association with thesuture loops means 28. This occurs without dependence upon additional support by thecatheter tip component 24. withdrawal of themovable component 58 moves the cutting element 78 through thesuture loop 76, cutting thesuture loop 76 and releasing the prosthesis 14 (asFig. 14B shows). - In yet another illustrative, alternative embodiment (see
Figs. 15A and 15B ), the restraining means 26 includes asingle tube 80 carried by thecentral shaft 22, through which themovable component 58 of the releasing means 28 passes. As thetube 74 shown inFigs. 14A and 14B , thetube 80 can comprise a surrounding tube of the type shown inFig. 12A (asFigs. 15A and 15B show) or an external tube of the type shown inFig. 12B . - -In this arrangement, the releasing
means 28 includes awedge element 84 carried on the distal end of themovable component 58 of the releasingmeans 28. Thewedge element 84 nests within amating wedge surface 86 formed in the proximal end of thecatheter tip component 24. Advancement of themovable component 58 moves thewedge element 84 into the registration within the wedge surface 86 (asFig. 15A shows) and out of registration with the wedge surface 86 (asFig. 15B shows). The releasing means 28 in this arrangement further includes alternative embodiments ofsuture loops 82 or 82', which are pinched between thewedge element 84 and thewedge surface 86 when theelement 84 and thesurface 86 are in registration, asFig. 15A shows. The embodiment of thesuture loop 82 comprises aclosed loop 82 carried by aprosthesis stent 48. The embodiment of the suture loop 82' comprises an open loop 82' carried by the proximal end of thecatheter tip component 24 and looped through aprosthesis stent 48. When either embodiment of thesuture loop 82 or 82' is pinched between thewedge element 84 and theindented surface 86, expansion of theprosthesis 14 is restrained (asFig. 15A shows). When themovable component 58 of the releasingmeans 28 is advanced proximally, thewedge element 84 is freed from registration within thewedge surface 86, freeing theloops 82 or 82', thereby releasing theprosthesis 14 for expansion, asFig. 15B shows. - The preferred embodiments of the invention are described above in detail for the purpose of setting forth a complete disclosure and for the sake of explanation and clarity.
- The above described embodiments of this invention are merely descriptive of its principles and are not to be limiting.
Claims (5)
- An endovascular prosthesis system comprising:a self-expanding stent prosthesis (14) for deployment in a blood vessel, the prosthesis having a distal end and a proximal end, the prosthesis being adapted to self expand from a radially reduced configuration to a radially enlarged configuration; andan apparatus for delivering the prosthesis comprising a catheter (10) sized and configured for introduction into the blood vessel, the catheter having a proximal end including a handle (20), a distal end including a shaft (22) for carrying the prosthesis, a releasing mechanism (28) for retaining at least a portion of the prosthesis in a radially compressed condition prior to deployment, a retaining mechanism (26) for maintaining the releasing mechanism in a desired relationship with the shaft, and a catheter tip component (24), an outer sheath (18) tapered between a larger distal diameter adjacent the catheter tip component and a smaller proximal diameter adjacent the proximal end of the catheter and movable in a proximal direction between an advanced position enclosing the prosthesis when in the radially reduced configuration and a withdrawn position free of the prosthesis, a spacer (30) for supporting the outer sheath, a first actuator (50) on the handle coupled to the tapered outer sheath, a second actuator (46) on the handle coupled to the releasing mechanism, the first actuator being operable to move the tapered outer sheath between the advanced and withdrawn positions, the second actuator being operable to actuate the release mechanism to release the distal end of the prosthesis from the carrier; anda fastener attachment assembly to introduce fasteners into the prosthesis to anchor the prosthesis in place.
- A system according to claim 1, wherein the releasing mechanism (28) includes a fastening member releasably securing the prosthesis (14) to the shaft (22).
- A system according to claim 2, wherein the fastening member comprises a wire (58).
- A system according to any one of claims 1 to 3, wherein the catheter (10) includes a lumen (36, 38) that accommodates passage of a guide wire (12).
- A system according to any preceding claim, wherein the prosthesis (14) comprises a malleable stent structure.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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US10/692,283 US7147657B2 (en) | 2003-10-23 | 2003-10-23 | Prosthesis delivery systems and methods |
PCT/US2004/027587 WO2005044073A2 (en) | 2003-10-23 | 2004-08-25 | Prosthesis delivery systems and methods |
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EP1682039A2 EP1682039A2 (en) | 2006-07-26 |
EP1682039A4 EP1682039A4 (en) | 2007-04-18 |
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US (3) | US7147657B2 (en) |
EP (1) | EP1682039B1 (en) |
JP (2) | JP4912883B2 (en) |
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AT (1) | ATE438362T1 (en) |
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Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9320591B2 (en) | 2001-11-28 | 2016-04-26 | Medtronic Vascular, Inc. | Devices, systems, and methods for prosthesis delivery and implantation, including the use of a fastener tool |
US10098770B2 (en) | 2001-11-28 | 2018-10-16 | Medtronic Vascular, Inc. | Endovascular aneurysm devices, systems, and methods |
Families Citing this family (187)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7491232B2 (en) * | 1998-09-18 | 2009-02-17 | Aptus Endosystems, Inc. | Catheter-based fastener implantation apparatus and methods with implantation force resolution |
AU2002325298A1 (en) | 2001-07-06 | 2003-01-21 | Angiomed Gmbh And Co. Medizintechnik Kg | Delivery system having a rapid pusher assembly for self-expanding stent, and stent exchange configuration |
GB0123633D0 (en) | 2001-10-02 | 2001-11-21 | Angiomed Ag | Stent delivery system |
CA2464048C (en) | 2001-11-28 | 2010-06-15 | Lee Bolduc | Endovascular aneurysm repair system |
US7147657B2 (en) | 2003-10-23 | 2006-12-12 | Aptus Endosystems, Inc. | Prosthesis delivery systems and methods |
US8231639B2 (en) | 2001-11-28 | 2012-07-31 | Aptus Endosystems, Inc. | Systems and methods for attaching a prosthesis within a body lumen or hollow organ |
US20090112302A1 (en) * | 2001-11-28 | 2009-04-30 | Josh Stafford | Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation |
US20050177180A1 (en) | 2001-11-28 | 2005-08-11 | Aptus Endosystems, Inc. | Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ |
US9320503B2 (en) | 2001-11-28 | 2016-04-26 | Medtronic Vascular, Inc. | Devices, system, and methods for guiding an operative tool into an interior body region |
US20110087320A1 (en) * | 2001-11-28 | 2011-04-14 | Aptus Endosystems, Inc. | Devices, Systems, and Methods for Prosthesis Delivery and Implantation, Including a Prosthesis Assembly |
DE60311806T2 (en) | 2002-06-11 | 2007-10-31 | Tyco Healthcare Group Lp, Norwalk | Clamp for attachment of Hernia mesh |
GB0327306D0 (en) * | 2003-11-24 | 2003-12-24 | Angiomed Gmbh & Co | Catheter device |
WO2004062458A2 (en) | 2003-01-15 | 2004-07-29 | Angiomed Gmbh & C0. Medizintechnik Kg | Trans-luminal surgical device |
US8926637B2 (en) | 2003-06-13 | 2015-01-06 | Covidien Lp | Multiple member interconnect for surgical instrument and absorbable screw fastener |
CA2527778C (en) | 2003-06-13 | 2011-11-08 | Tyco Healthcare Group Lp | Multiple member interconnect for surgical instrument and absorbable screw fastener |
US11259945B2 (en) | 2003-09-03 | 2022-03-01 | Bolton Medical, Inc. | Dual capture device for stent graft delivery system and method for capturing a stent graft |
US9198786B2 (en) | 2003-09-03 | 2015-12-01 | Bolton Medical, Inc. | Lumen repair device with capture structure |
US8500792B2 (en) | 2003-09-03 | 2013-08-06 | Bolton Medical, Inc. | Dual capture device for stent graft delivery system and method for capturing a stent graft |
US20080264102A1 (en) | 2004-02-23 | 2008-10-30 | Bolton Medical, Inc. | Sheath Capture Device for Stent Graft Delivery System and Method for Operating Same |
US20070198078A1 (en) | 2003-09-03 | 2007-08-23 | Bolton Medical, Inc. | Delivery system and method for self-centering a Proximal end of a stent graft |
US11596537B2 (en) | 2003-09-03 | 2023-03-07 | Bolton Medical, Inc. | Delivery system and method for self-centering a proximal end of a stent graft |
US7763063B2 (en) | 2003-09-03 | 2010-07-27 | Bolton Medical, Inc. | Self-aligning stent graft delivery system, kit, and method |
US8292943B2 (en) | 2003-09-03 | 2012-10-23 | Bolton Medical, Inc. | Stent graft with longitudinal support member |
US10478179B2 (en) | 2004-04-27 | 2019-11-19 | Covidien Lp | Absorbable fastener for hernia mesh fixation |
AU2005262541B2 (en) * | 2004-06-16 | 2011-04-21 | Cook Incorporated | Thoracic deployment device and stent graft |
US7462185B1 (en) * | 2004-12-23 | 2008-12-09 | Cardican Inc. | Intravascular stapling tool |
US7678121B1 (en) | 2004-12-23 | 2010-03-16 | Cardica, Inc. | Surgical stapling tool |
WO2006097931A2 (en) | 2005-03-17 | 2006-09-21 | Valtech Cardio, Ltd. | Mitral valve treatment techniques |
US7344544B2 (en) | 2005-03-28 | 2008-03-18 | Cardica, Inc. | Vascular closure system |
US8333777B2 (en) | 2005-04-22 | 2012-12-18 | Benvenue Medical, Inc. | Catheter-based tissue remodeling devices and methods |
US8951285B2 (en) | 2005-07-05 | 2015-02-10 | Mitralign, Inc. | Tissue anchor, anchoring system and methods of using the same |
US8123795B1 (en) | 2005-10-03 | 2012-02-28 | Cardica, Inc. | System for attaching an abdominal aortic stent or the like |
WO2007134290A2 (en) * | 2006-05-12 | 2007-11-22 | Ev3, Inc. | Implant and delivery system with multiple marker interlocks |
EP3360509B1 (en) | 2006-07-31 | 2022-06-22 | Syntheon TAVR, LLC | Sealable endovascular implants |
US9585743B2 (en) | 2006-07-31 | 2017-03-07 | Edwards Lifesciences Cardiaq Llc | Surgical implant devices and methods for their manufacture and use |
US7875053B2 (en) * | 2006-09-15 | 2011-01-25 | Cardica, Inc. | Apparatus and method for closure of patent foramen ovale |
AU2007325652B2 (en) * | 2006-11-30 | 2012-07-12 | Cook Medical Technologies Llc | Implant release mechanism |
US9974653B2 (en) | 2006-12-05 | 2018-05-22 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
US11259924B2 (en) | 2006-12-05 | 2022-03-01 | Valtech Cardio Ltd. | Implantation of repair devices in the heart |
US11660190B2 (en) | 2007-03-13 | 2023-05-30 | Edwards Lifesciences Corporation | Tissue anchors, systems and methods, and devices |
US9149379B2 (en) * | 2007-07-16 | 2015-10-06 | Cook Medical Technologies Llc | Delivery device |
US9566178B2 (en) * | 2010-06-24 | 2017-02-14 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
WO2009023221A1 (en) * | 2007-08-13 | 2009-02-19 | William A. Cook Australia Pty. Ltd. | Deployment device |
CN101861134B (en) * | 2007-09-11 | 2013-06-26 | 彼鲁兹实验室 | Device for treating a blood circulation conduit |
US20090093826A1 (en) * | 2007-10-05 | 2009-04-09 | Cardica, Inc. | Patent Foramen Ovale Closure System |
US8574284B2 (en) | 2007-12-26 | 2013-11-05 | Cook Medical Technologies Llc | Low profile non-symmetrical bare alignment stents with graft |
GB2475494B (en) | 2009-11-18 | 2011-11-23 | Cook William Europ | Stent graft and introducer assembly |
US9180030B2 (en) | 2007-12-26 | 2015-11-10 | Cook Medical Technologies Llc | Low profile non-symmetrical stent |
GB2476451A (en) | 2009-11-19 | 2011-06-29 | Cook William Europ | Stent Graft |
US9226813B2 (en) | 2007-12-26 | 2016-01-05 | Cook Medical Technologies Llc | Low profile non-symmetrical stent |
US8382829B1 (en) | 2008-03-10 | 2013-02-26 | Mitralign, Inc. | Method to reduce mitral regurgitation by cinching the commissure of the mitral valve |
US10813779B2 (en) * | 2008-04-25 | 2020-10-27 | CARDINAL HEALTH SWITZERLAND 515 GmbH | Stent attachment and deployment mechanism |
WO2009148594A1 (en) | 2008-06-04 | 2009-12-10 | Gore Enterprise Holdings, Inc. | Controlled deployable medical device and method of making the same |
EP2282705A1 (en) * | 2008-06-04 | 2011-02-16 | Gore Enterprise Holdings, Inc. | Controlled deployable medical device and method of making the same |
GB0810749D0 (en) | 2008-06-11 | 2008-07-16 | Angiomed Ag | Catherter delivery device |
US9750625B2 (en) | 2008-06-11 | 2017-09-05 | C.R. Bard, Inc. | Catheter delivery device |
BRPI0913877A2 (en) * | 2008-06-30 | 2015-10-27 | Bolton Medical Inc | abdominal aortic aneurysms: systems and methods of use |
US8652202B2 (en) | 2008-08-22 | 2014-02-18 | Edwards Lifesciences Corporation | Prosthetic heart valve and delivery apparatus |
ES2409693T3 (en) | 2008-10-10 | 2013-06-27 | Sadra Medical, Inc. | Medical devices and supply systems to supply medical devices |
CA2740867C (en) | 2008-10-16 | 2018-06-12 | Aptus Endosystems, Inc. | Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation |
US8241351B2 (en) | 2008-12-22 | 2012-08-14 | Valtech Cardio, Ltd. | Adjustable partial annuloplasty ring and mechanism therefor |
ES2873182T3 (en) | 2008-12-22 | 2021-11-03 | Valtech Cardio Ltd | Adjustable annuloplasty devices |
US8715342B2 (en) | 2009-05-07 | 2014-05-06 | Valtech Cardio, Ltd. | Annuloplasty ring with intra-ring anchoring |
US10517719B2 (en) | 2008-12-22 | 2019-12-31 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
US8545553B2 (en) | 2009-05-04 | 2013-10-01 | Valtech Cardio, Ltd. | Over-wire rotation tool |
AU2009335031B2 (en) * | 2008-12-30 | 2013-07-25 | Cook Medical Technologies Llc | Delivery device |
US20100174292A1 (en) * | 2009-01-07 | 2010-07-08 | Vanderbilt University | Surgical instrument for placing a prosthesis into a target area of a living subject |
US8858610B2 (en) | 2009-01-19 | 2014-10-14 | W. L. Gore & Associates, Inc. | Forced deployment sequence |
US8876807B2 (en) | 2009-01-19 | 2014-11-04 | W. L. Gore & Associates, Inc. | Forced deployment sequence |
US20100204717A1 (en) * | 2009-02-12 | 2010-08-12 | Cardica, Inc. | Surgical Device for Multiple Clip Application |
US8353956B2 (en) | 2009-02-17 | 2013-01-15 | Valtech Cardio, Ltd. | Actively-engageable movement-restriction mechanism for use with an annuloplasty structure |
EP2405868B1 (en) | 2009-03-13 | 2017-06-28 | Bolton Medical Inc. | System for deploying an endoluminal prosthesis at a surgical site |
GB2469072A (en) * | 2009-03-31 | 2010-10-06 | Royal Brompton & Harefield Nhs | Guidewire with Anchor for a catheter |
US7875029B1 (en) | 2009-05-04 | 2011-01-25 | Cardica, Inc. | Surgical device switchable between clip application and coagulation modes |
US9968452B2 (en) | 2009-05-04 | 2018-05-15 | Valtech Cardio, Ltd. | Annuloplasty ring delivery cathethers |
EP2436343B1 (en) * | 2009-05-27 | 2017-02-08 | Kawasumi Laboratories, Inc. | Placement device for tubular medical treatment instrument and front tip of placement device for tubular medical treatment instrument |
US8771333B2 (en) | 2009-06-23 | 2014-07-08 | Cordis Corporation | Stent-graft securement device |
US9180007B2 (en) | 2009-10-29 | 2015-11-10 | Valtech Cardio, Ltd. | Apparatus and method for guide-wire based advancement of an adjustable implant |
US10098737B2 (en) | 2009-10-29 | 2018-10-16 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US9757263B2 (en) | 2009-11-18 | 2017-09-12 | Cook Medical Technologies Llc | Stent graft and introducer assembly |
DE102009055969A1 (en) * | 2009-11-27 | 2011-06-01 | Transcatheter Technologies Gmbh | Device and set for folding or unfolding a medical implant and method |
EP2559403B1 (en) | 2009-12-01 | 2016-05-04 | Altura Medical, Inc. | Modular endograft devices |
EP2506777B1 (en) | 2009-12-02 | 2020-11-25 | Valtech Cardio, Ltd. | Combination of spool assembly coupled to a helical anchor and delivery tool for implantation thereof |
WO2011094527A1 (en) * | 2010-01-29 | 2011-08-04 | Cook Medical Technologies Llc | Mechanically expandable delivery and dilation systems |
US8926692B2 (en) * | 2010-04-09 | 2015-01-06 | Medtronic, Inc. | Transcatheter prosthetic heart valve delivery device with partial deployment and release features and methods |
WO2011163386A1 (en) | 2010-06-24 | 2011-12-29 | Cordis Corporation | Apparatus for and method of pulling a tensile member from a medical device |
JP5597309B2 (en) | 2010-07-30 | 2014-10-01 | クック メディカル テクノロジーズ エルエルシー | Prosthesis placement equipment with controlled release and recovery |
US10321998B2 (en) | 2010-09-23 | 2019-06-18 | Transmural Systems Llc | Methods and systems for delivering prostheses using rail techniques |
GB2485762B (en) * | 2010-11-12 | 2012-12-05 | Cook Medical Technologies Llc | Introducer assembly and dilator tip therefor |
JP2012139471A (en) * | 2011-01-06 | 2012-07-26 | Nippon Zeon Co Ltd | Stent delivery apparatus |
US9744033B2 (en) | 2011-04-01 | 2017-08-29 | W.L. Gore & Associates, Inc. | Elastomeric leaflet for prosthetic heart valves |
US10117765B2 (en) | 2011-06-14 | 2018-11-06 | W.L. Gore Associates, Inc | Apposition fiber for use in endoluminal deployment of expandable implants |
US10792152B2 (en) | 2011-06-23 | 2020-10-06 | Valtech Cardio, Ltd. | Closed band for percutaneous annuloplasty |
US9554806B2 (en) | 2011-09-16 | 2017-01-31 | W. L. Gore & Associates, Inc. | Occlusive devices |
US9549817B2 (en) * | 2011-09-22 | 2017-01-24 | Transmural Systems Llc | Devices, systems and methods for repairing lumenal systems |
US9827093B2 (en) | 2011-10-21 | 2017-11-28 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
US8945146B2 (en) | 2011-10-24 | 2015-02-03 | Medtronic, Inc. | Delivery system assemblies and associated methods for implantable medical devices |
US8858623B2 (en) | 2011-11-04 | 2014-10-14 | Valtech Cardio, Ltd. | Implant having multiple rotational assemblies |
EP2775896B1 (en) | 2011-11-08 | 2020-01-01 | Valtech Cardio, Ltd. | Controlled steering functionality for implant-delivery tool |
US9782282B2 (en) | 2011-11-14 | 2017-10-10 | W. L. Gore & Associates, Inc. | External steerable fiber for use in endoluminal deployment of expandable devices |
US9877858B2 (en) | 2011-11-14 | 2018-01-30 | W. L. Gore & Associates, Inc. | External steerable fiber for use in endoluminal deployment of expandable devices |
US8721587B2 (en) | 2011-11-17 | 2014-05-13 | Medtronic, Inc. | Delivery system assemblies and associated methods for implantable medical devices |
US9216293B2 (en) | 2011-11-17 | 2015-12-22 | Medtronic, Inc. | Delivery system assemblies for implantable medical devices |
CN102488576B (en) * | 2011-11-25 | 2014-07-16 | 北京华脉泰科医疗器械有限公司 | Convey and release device for covered stents |
CN104203157B (en) | 2011-12-12 | 2016-02-03 | 戴维·阿隆 | Heart valve repair apparatus |
US9510945B2 (en) * | 2011-12-20 | 2016-12-06 | Boston Scientific Scimed Inc. | Medical device handle |
AU2013222451B2 (en) | 2012-02-22 | 2018-08-09 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
US9375308B2 (en) | 2012-03-13 | 2016-06-28 | W. L. Gore & Associates, Inc. | External steerable fiber for use in endoluminal deployment of expandable devices |
WO2013154749A1 (en) | 2012-04-12 | 2013-10-17 | Bolton Medical, Inc. | Vascular prosthetic delivery device and method of use |
JP6118894B2 (en) * | 2012-05-16 | 2017-04-19 | エッチエルティ インコーポレイテッドHlt, Inc. | Inverted transfer device and method for prosthesis |
US9144510B2 (en) | 2012-06-13 | 2015-09-29 | Cook Medical Technologies Llc | Systems and methods for deploying a portion of a stent using at least one coiled member |
US9364355B2 (en) | 2012-06-13 | 2016-06-14 | Cook Medical Technologies Llc | Systems and methods for deploying a portion of a stent using at least one coiled member |
US20140046429A1 (en) | 2012-08-10 | 2014-02-13 | Altura Medical, Inc. | Stent delivery systems and associated methods |
EP2900150B1 (en) | 2012-09-29 | 2018-04-18 | Mitralign, Inc. | Plication lock delivery system |
US10376266B2 (en) | 2012-10-23 | 2019-08-13 | Valtech Cardio, Ltd. | Percutaneous tissue anchor techniques |
EP3730084A1 (en) | 2012-10-23 | 2020-10-28 | Valtech Cardio, Ltd. | Controlled steering functionality for implant-delivery tool |
US9730793B2 (en) | 2012-12-06 | 2017-08-15 | Valtech Cardio, Ltd. | Techniques for guide-wire based advancement of a tool |
US9655756B2 (en) | 2012-12-21 | 2017-05-23 | Cook Medical Technologies Llc | Systems and methods for deploying a portion of a stent using an auger-style device |
US9687373B2 (en) | 2012-12-21 | 2017-06-27 | Cook Medical Technologies Llc | Systems and methods for securing and releasing a portion of a stent |
US10350096B2 (en) * | 2012-12-26 | 2019-07-16 | Cook Medical Technologies Llc | Expandable stent-graft system having diameter reducing connectors |
US9351733B2 (en) | 2013-01-18 | 2016-05-31 | Covidien Lp | Surgical fastener applier |
EP2961351B1 (en) | 2013-02-26 | 2018-11-28 | Mitralign, Inc. | Devices for percutaneous tricuspid valve repair |
US9358010B2 (en) | 2013-03-12 | 2016-06-07 | Covidien Lp | Flex cable and spring-loaded tube for tacking device |
US9308108B2 (en) | 2013-03-13 | 2016-04-12 | Cook Medical Technologies Llc | Controlled release and recapture stent-deployment device |
US10449333B2 (en) | 2013-03-14 | 2019-10-22 | Valtech Cardio, Ltd. | Guidewire feeder |
US9867620B2 (en) | 2013-03-14 | 2018-01-16 | Covidien Lp | Articulation joint for apparatus for endoscopic procedures |
US9737426B2 (en) | 2013-03-15 | 2017-08-22 | Altura Medical, Inc. | Endograft device delivery systems and associated methods |
US9439751B2 (en) | 2013-03-15 | 2016-09-13 | Bolton Medical, Inc. | Hemostasis valve and delivery systems |
WO2014152503A1 (en) | 2013-03-15 | 2014-09-25 | Mitralign, Inc. | Translation catheters, systems, and methods of use thereof |
US11911258B2 (en) | 2013-06-26 | 2024-02-27 | W. L. Gore & Associates, Inc. | Space filling devices |
US10085746B2 (en) | 2013-06-28 | 2018-10-02 | Covidien Lp | Surgical instrument including rotating end effector and rotation-limiting structure |
US9358004B2 (en) | 2013-06-28 | 2016-06-07 | Covidien Lp | Articulating apparatus for endoscopic procedures |
US9351728B2 (en) | 2013-06-28 | 2016-05-31 | Covidien Lp | Articulating apparatus for endoscopic procedures |
US9668730B2 (en) | 2013-06-28 | 2017-06-06 | Covidien Lp | Articulating apparatus for endoscopic procedures with timing system |
US20150032130A1 (en) | 2013-07-24 | 2015-01-29 | Covidien Lp | Expanding absorbable tack |
US10070857B2 (en) | 2013-08-31 | 2018-09-11 | Mitralign, Inc. | Devices and methods for locating and implanting tissue anchors at mitral valve commissure |
US9925045B2 (en) | 2013-10-21 | 2018-03-27 | Medtronic Vascular Galway | Systems, devices and methods for transcatheter valve delivery |
US10299793B2 (en) | 2013-10-23 | 2019-05-28 | Valtech Cardio, Ltd. | Anchor magazine |
US9610162B2 (en) | 2013-12-26 | 2017-04-04 | Valtech Cardio, Ltd. | Implantation of flexible implant |
US10058315B2 (en) | 2014-03-27 | 2018-08-28 | Transmural Systems Llc | Devices and methods for closure of transvascular or transcameral access ports |
WO2015149292A1 (en) | 2014-04-02 | 2015-10-08 | Covidien Lp | Surgical fastener applying apparatus, kits and methods for endoscopic procedures |
FR3023703B1 (en) | 2014-07-17 | 2021-01-29 | Cormove | BLOOD CIRCULATION DUCT TREATMENT DEVICE |
US10195030B2 (en) | 2014-10-14 | 2019-02-05 | Valtech Cardio, Ltd. | Leaflet-restraining techniques |
US10016293B2 (en) | 2014-12-29 | 2018-07-10 | Cook Medical Technologies Llc | Prosthesis delivery systems having an atraumatic tip for use with trigger wires |
KR102501552B1 (en) | 2015-01-11 | 2023-03-21 | 어씨러스 메디컬, 엘엘씨 | Hybrid device for surgical aortic repair |
US20160256269A1 (en) | 2015-03-05 | 2016-09-08 | Mitralign, Inc. | Devices for treating paravalvular leakage and methods use thereof |
EP3283019A1 (en) | 2015-04-13 | 2018-02-21 | Cook Medical Technologies LLC | Axial lock and release stent deployment system |
CN111265335B (en) | 2015-04-30 | 2022-03-15 | 瓦尔泰克卡迪欧有限公司 | Valvuloplasty techniques |
JP2018515246A (en) | 2015-05-14 | 2018-06-14 | ダブリュ.エル.ゴア アンド アソシエイツ,インコーポレイティドW.L. Gore & Associates, Incorporated | Devices and methods for atrial appendage occlusion |
US10299950B2 (en) * | 2015-05-20 | 2019-05-28 | Cook Medical Technologies Llc | Stent delivery system |
ES2921535T3 (en) | 2015-06-18 | 2022-08-29 | Ascyrus Medical Llc | Branch aortic graft |
US10779940B2 (en) | 2015-09-03 | 2020-09-22 | Boston Scientific Scimed, Inc. | Medical device handle |
US10426482B2 (en) | 2015-09-15 | 2019-10-01 | The United States Of America, As Represented By The Secretary, Department Of Health And Human Services | Devices and methods for effectuating percutaneous Glenn and Fontan procedures |
WO2017117370A2 (en) | 2015-12-30 | 2017-07-06 | Mitralign, Inc. | System and method for reducing tricuspid regurgitation |
US10751182B2 (en) | 2015-12-30 | 2020-08-25 | Edwards Lifesciences Corporation | System and method for reshaping right heart |
US11219746B2 (en) | 2016-03-21 | 2022-01-11 | Edwards Lifesciences Corporation | Multi-direction steerable handles for steering catheters |
US10799677B2 (en) | 2016-03-21 | 2020-10-13 | Edwards Lifesciences Corporation | Multi-direction steerable handles for steering catheters |
US10799676B2 (en) | 2016-03-21 | 2020-10-13 | Edwards Lifesciences Corporation | Multi-direction steerable handles for steering catheters |
US10702274B2 (en) | 2016-05-26 | 2020-07-07 | Edwards Lifesciences Corporation | Method and system for closing left atrial appendage |
GB201611910D0 (en) | 2016-07-08 | 2016-08-24 | Valtech Cardio Ltd | Adjustable annuloplasty device with alternating peaks and troughs |
US10743859B2 (en) | 2016-10-21 | 2020-08-18 | Covidien Lp | Surgical end effectors |
US10617409B2 (en) | 2016-10-21 | 2020-04-14 | Covidien Lp | Surgical end effectors |
US11298123B2 (en) | 2016-10-21 | 2022-04-12 | Covidien Lp | Surgical end effectors |
US10888309B2 (en) | 2017-01-31 | 2021-01-12 | Covidien Lp | Surgical fastener devices with geometric tubes |
WO2018175048A1 (en) | 2017-03-24 | 2018-09-27 | Ascyrus Medical, Llc | Multi-spiral self-expanding stent and methods of making and using the same |
US11224511B2 (en) | 2017-04-18 | 2022-01-18 | Edwards Lifesciences Corporation | Heart valve sealing devices and delivery devices therefor |
US11045627B2 (en) | 2017-04-18 | 2021-06-29 | Edwards Lifesciences Corporation | Catheter system with linear actuation control mechanism |
SI3682854T1 (en) | 2017-04-18 | 2022-04-29 | Edwards Lifesciences Corporation | Heart valve sealing devices and delivery devices therefor |
US10959846B2 (en) | 2017-05-10 | 2021-03-30 | Edwards Lifesciences Corporation | Mitral valve spacer device |
US11173023B2 (en) | 2017-10-16 | 2021-11-16 | W. L. Gore & Associates, Inc. | Medical devices and anchors therefor |
US10835221B2 (en) | 2017-11-02 | 2020-11-17 | Valtech Cardio, Ltd. | Implant-cinching devices and systems |
US11135062B2 (en) | 2017-11-20 | 2021-10-05 | Valtech Cardio Ltd. | Cinching of dilated heart muscle |
CN111655200B (en) | 2018-01-24 | 2023-07-14 | 爱德华兹生命科学创新(以色列)有限公司 | Contraction of annuloplasty structures |
EP3743014B1 (en) | 2018-01-26 | 2023-07-19 | Edwards Lifesciences Innovation (Israel) Ltd. | Techniques for facilitating heart valve tethering and chord replacement |
US11298126B2 (en) | 2018-05-02 | 2022-04-12 | Covidien Lp | Shipping wedge for end effector installation onto surgical devices |
US11116500B2 (en) | 2018-06-28 | 2021-09-14 | Covidien Lp | Surgical fastener applying device, kits and methods for endoscopic procedures |
CN112384175A (en) | 2018-07-12 | 2021-02-19 | 瓦尔泰克卡迪欧有限公司 | Annuloplasty system and locking tool therefor |
US11523817B2 (en) | 2019-06-27 | 2022-12-13 | Covidien Lp | Endoluminal pursestring device |
EP4051182A1 (en) | 2019-10-29 | 2022-09-07 | Edwards Lifesciences Innovation (Israel) Ltd. | Annuloplasty and tissue anchor technologies |
USD944984S1 (en) | 2019-12-19 | 2022-03-01 | Covidien Lp | Tubular positioning guide |
USD944985S1 (en) | 2019-12-19 | 2022-03-01 | Covidien Lp | Positioning guide cuff |
US11197675B2 (en) | 2019-12-19 | 2021-12-14 | Covidien Lp | Positioning guide for surgical instruments and surgical instrument systems |
WO2021236634A2 (en) | 2020-05-20 | 2021-11-25 | Cardiac Implants, Llc | Reducing the diameter of a cardiac valve annulus with independent control over each of the anchors that are launched into the annulus |
WO2022191209A1 (en) * | 2021-03-12 | 2022-09-15 | Sbカワスミ株式会社 | Catheter and delivery system |
CN115770131A (en) * | 2021-09-07 | 2023-03-10 | 上海蓝脉医疗科技有限公司 | Conveying system |
WO2023163122A1 (en) * | 2022-02-28 | 2023-08-31 | Sbカワスミ株式会社 | Catheter and delivery system |
US20240033068A1 (en) * | 2022-07-28 | 2024-02-01 | Medtronic Vascular, Inc. | Endovascular stent graft cover with torsion layer |
Family Cites Families (114)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2033039A (en) | 1935-05-22 | 1936-03-03 | Arthur A Limpert | Double point rotary pin |
US3499222A (en) | 1965-08-17 | 1970-03-10 | Leonard I Linkow | Intra-osseous pins and posts and their use and techniques thereof |
US3686740A (en) | 1970-06-19 | 1972-08-29 | Donald P Shiley | Method of assemblying a sutureless heart valve |
US3799172A (en) | 1972-09-25 | 1974-03-26 | R Szpur | Retention catheter |
FR2299548A1 (en) | 1975-01-30 | 1976-08-27 | Melin Raymond | Wire attachment element for corrugated cardboard cartons - has corkscrew form with bevelled end and insertion tool with chuck to match |
US4140126A (en) | 1977-02-18 | 1979-02-20 | Choudhury M Hasan | Method for performing aneurysm repair |
US4307722A (en) | 1979-08-14 | 1981-12-29 | Evans Joseph M | Dilators for arterial dilation |
DE3333427A1 (en) | 1983-09-16 | 1985-04-04 | Karl M. Reich Maschinenfabrik GmbH, 7440 Nürtingen | SCREW-IN DEVICE |
US5669936A (en) | 1983-12-09 | 1997-09-23 | Endovascular Technologies, Inc. | Endovascular grafting system and method for use therewith |
US5104399A (en) | 1986-12-10 | 1992-04-14 | Endovascular Technologies, Inc. | Artificial graft and implantation method |
US5693083A (en) * | 1983-12-09 | 1997-12-02 | Endovascular Technologies, Inc. | Thoracic graft and delivery catheter |
US4580568A (en) | 1984-10-01 | 1986-04-08 | Cook, Incorporated | Percutaneous endovascular stent and method for insertion thereof |
US4781682A (en) | 1987-08-13 | 1988-11-01 | Patel Piyush V | Catheter having support flaps and method of inserting catheter |
FR2624747A1 (en) | 1987-12-18 | 1989-06-23 | Delsanti Gerard | REMOVABLE ENDO-ARTERIAL DEVICES FOR REPAIRING ARTERIAL WALL DECOLLEMENTS |
US4921484A (en) | 1988-07-25 | 1990-05-01 | Cordis Corporation | Mesh balloon catheter device |
US4898577A (en) | 1988-09-28 | 1990-02-06 | Advanced Cardiovascular Systems, Inc. | Guiding cathether with controllable distal tip |
US5030204A (en) | 1988-09-28 | 1991-07-09 | Advanced Cardiovascular Systems, Inc. | Guiding catheter with controllable distal tip |
SE8803444D0 (en) | 1988-09-28 | 1988-09-28 | Medinvent Sa | A DEVICE FOR TRANSLUMINAL IMPLANTATION OR EXTRACTION |
US5480382A (en) | 1989-01-09 | 1996-01-02 | Pilot Cardiovascular Systems, Inc. | Steerable medical device |
US5053047A (en) | 1989-05-16 | 1991-10-01 | Inbae Yoon | Suture devices particularly useful in endoscopic surgery and methods of suturing |
US5207695A (en) | 1989-06-19 | 1993-05-04 | Trout Iii Hugh H | Aortic graft, implantation device, and method for repairing aortic aneurysm |
US5254088A (en) | 1990-02-02 | 1993-10-19 | Ep Technologies, Inc. | Catheter steering mechanism |
US5071407A (en) | 1990-04-12 | 1991-12-10 | Schneider (U.S.A.) Inc. | Radially expandable fixation member |
US5360443A (en) | 1990-06-11 | 1994-11-01 | Barone Hector D | Aortic graft for repairing an abdominal aortic aneurysm |
US5578071A (en) | 1990-06-11 | 1996-11-26 | Parodi; Juan C. | Aortic graft |
AU633453B2 (en) | 1990-10-09 | 1993-01-28 | Cook Incorporated | Percutaneous stent assembly |
US5042707A (en) | 1990-10-16 | 1991-08-27 | Taheri Syde A | Intravascular stapler, and method of operating same |
CA2202800A1 (en) | 1991-04-11 | 1992-10-12 | Alec A. Piplani | Endovascular graft having bifurcation and apparatus and method for deploying the same |
US5456714A (en) | 1991-07-04 | 1995-10-10 | Owen; Earl R. | Tubular surgical implant having a locking ring and flange |
US5766151A (en) | 1991-07-16 | 1998-06-16 | Heartport, Inc. | Endovascular system for arresting the heart |
US5693084A (en) | 1991-10-25 | 1997-12-02 | Cook Incorporated | Expandable transluminal graft prosthesis for repair of aneurysm |
US5387235A (en) | 1991-10-25 | 1995-02-07 | Cook Incorporated | Expandable transluminal graft prosthesis for repair of aneurysm |
US5456713A (en) | 1991-10-25 | 1995-10-10 | Cook Incorporated | Expandable transluminal graft prosthesis for repairs of aneurysm and method for implanting |
CA2081424C (en) | 1991-10-25 | 2008-12-30 | Timothy A. Chuter | Expandable transluminal graft prosthesis for repair of aneurysm |
US5330490A (en) | 1992-04-10 | 1994-07-19 | Wilk Peter J | Endoscopic device, prosthesis and method for use in endovascular repair |
US5290295A (en) | 1992-07-15 | 1994-03-01 | Querals & Fine, Inc. | Insertion tool for an intraluminal graft procedure |
US5707376A (en) | 1992-08-06 | 1998-01-13 | William Cook Europe A/S | Stent introducer and method of use |
US5702365A (en) | 1992-09-08 | 1997-12-30 | King; Toby St. John | Daul-lumen catheter |
US5480423A (en) * | 1993-05-20 | 1996-01-02 | Boston Scientific Corporation | Prosthesis delivery |
US5639278A (en) | 1993-10-21 | 1997-06-17 | Corvita Corporation | Expandable supportive bifurcated endoluminal grafts |
DE69419877T2 (en) * | 1993-11-04 | 1999-12-16 | C.R. Bard, Inc. | Fixed vascular prosthesis |
AU1011595A (en) | 1994-01-13 | 1995-07-20 | Ethicon Inc. | Spiral surgical tack |
US5609627A (en) | 1994-02-09 | 1997-03-11 | Boston Scientific Technology, Inc. | Method for delivering a bifurcated endoluminal prosthesis |
US6165210A (en) | 1994-04-01 | 2000-12-26 | Gore Enterprise Holdings, Inc. | Self-expandable helical intravascular stent and stent-graft |
US5470337A (en) | 1994-05-17 | 1995-11-28 | Moss; Gerald | Surgical fastener |
US5683451A (en) | 1994-06-08 | 1997-11-04 | Cardiovascular Concepts, Inc. | Apparatus and methods for deployment release of intraluminal prostheses |
US5824041A (en) | 1994-06-08 | 1998-10-20 | Medtronic, Inc. | Apparatus and methods for placement and repositioning of intraluminal prostheses |
US5582616A (en) | 1994-08-05 | 1996-12-10 | Origin Medsystems, Inc. | Surgical helical fastener with applicator |
US5972023A (en) | 1994-08-15 | 1999-10-26 | Eva Corporation | Implantation device for an aortic graft method of treating aortic aneurysm |
US6015429A (en) * | 1994-09-08 | 2000-01-18 | Gore Enterprise Holdings, Inc. | Procedures for introducing stents and stent-grafts |
US5683449A (en) | 1995-02-24 | 1997-11-04 | Marcade; Jean Paul | Modular bifurcated intraluminal grafts and methods for delivering and assembling same |
US5662675A (en) | 1995-02-24 | 1997-09-02 | Intervascular, Inc. | Delivery catheter assembly |
JP3260583B2 (en) * | 1995-04-04 | 2002-02-25 | 株式会社東芝 | Dynamic semiconductor memory and test method thereof |
US5626613A (en) | 1995-05-04 | 1997-05-06 | Arthrex, Inc. | Corkscrew suture anchor and driver |
US5534007A (en) * | 1995-05-18 | 1996-07-09 | Scimed Life Systems, Inc. | Stent deployment catheter with collapsible sheath |
US5700269A (en) | 1995-06-06 | 1997-12-23 | Corvita Corporation | Endoluminal prosthesis deployment device for use with prostheses of variable length and having retraction ability |
US5713907A (en) | 1995-07-20 | 1998-02-03 | Endotex Interventional Systems, Inc. | Apparatus and method for dilating a lumen and for inserting an intraluminal graft |
US5662683A (en) | 1995-08-22 | 1997-09-02 | Ortho Helix Limited | Open helical organic tissue anchor and method of facilitating healing |
US6193745B1 (en) | 1995-10-03 | 2001-02-27 | Medtronic, Inc. | Modular intraluminal prosteheses construction and methods |
US6287315B1 (en) | 1995-10-30 | 2001-09-11 | World Medical Manufacturing Corporation | Apparatus for delivering an endoluminal prosthesis |
KR100244996B1 (en) | 1995-12-25 | 2000-02-15 | 이마이 기요스케 | Relaxation inducing device |
US5749921A (en) | 1996-02-20 | 1998-05-12 | Medtronic, Inc. | Apparatus and methods for compression of endoluminal prostheses |
US5676697A (en) | 1996-07-29 | 1997-10-14 | Cardiovascular Dynamics, Inc. | Two-piece, bifurcated intraluminal graft for repair of aneurysm |
US6258119B1 (en) | 1996-11-07 | 2001-07-10 | Myocardial Stents, Inc. | Implant device for trans myocardial revascularization |
US5993466A (en) | 1997-06-17 | 1999-11-30 | Yoon; Inbae | Suturing instrument with multiple rotatably mounted spreadable needle holders |
US5776142A (en) | 1996-12-19 | 1998-07-07 | Medtronic, Inc. | Controllable stent delivery system and method |
US5968053A (en) | 1997-01-31 | 1999-10-19 | Cardiac Assist Technologies, Inc. | Method and apparatus for implanting a graft in a vessel of a patient |
US5855565A (en) | 1997-02-21 | 1999-01-05 | Bar-Cohen; Yaniv | Cardiovascular mechanically expanding catheter |
US5830229A (en) * | 1997-03-07 | 1998-11-03 | Micro Therapeutics Inc. | Hoop stent |
US6086582A (en) | 1997-03-13 | 2000-07-11 | Altman; Peter A. | Cardiac drug delivery system |
US6048360A (en) | 1997-03-18 | 2000-04-11 | Endotex Interventional Systems, Inc. | Methods of making and using coiled sheet graft for single and bifurcated lumens |
AUPO700897A0 (en) * | 1997-05-26 | 1997-06-19 | William A Cook Australia Pty Ltd | A method and means of deploying a graft |
US5944750A (en) | 1997-06-30 | 1999-08-31 | Eva Corporation | Method and apparatus for the surgical repair of aneurysms |
US6248118B1 (en) | 1997-06-30 | 2001-06-19 | Eva Corporation | Heat activated surgical fastener |
US6270516B1 (en) | 1997-06-30 | 2001-08-07 | Eva Corporation | Repair apparatus for use in surgical procedures |
US5957940A (en) | 1997-06-30 | 1999-09-28 | Eva Corporation | Fasteners for use in the surgical repair of aneurysms |
US5906619A (en) | 1997-07-24 | 1999-05-25 | Medtronic, Inc. | Disposable delivery device for endoluminal prostheses |
US6070589A (en) | 1997-08-01 | 2000-06-06 | Teramed, Inc. | Methods for deploying bypass graft stents |
US6306164B1 (en) | 1997-09-05 | 2001-10-23 | C. R. Bard, Inc. | Short body endoprosthesis |
US5984955A (en) | 1997-09-11 | 1999-11-16 | Wisselink; Willem | System and method for endoluminal grafting of bifurcated or branched vessels |
US5980548A (en) | 1997-10-29 | 1999-11-09 | Kensey Nash Corporation | Transmyocardial revascularization system |
US6395019B2 (en) | 1998-02-09 | 2002-05-28 | Trivascular, Inc. | Endovascular graft |
US8075570B2 (en) | 2001-11-28 | 2011-12-13 | Aptus Endosystems, Inc. | Intraluminal prosthesis attachment systems and methods |
CA2265136C (en) | 1998-03-13 | 2008-09-09 | Juan Carlos Parodi | Endovascular device for application of prostheses with sutures |
US6217597B1 (en) | 1998-07-24 | 2001-04-17 | Eva Corporation | Surgical cutting device and method of using the same |
US6145509A (en) | 1998-07-24 | 2000-11-14 | Eva Corporation | Depth sensor device for use in a surgical procedure |
US6544253B1 (en) | 1998-07-24 | 2003-04-08 | Eva Corporation | Surgical support device and method of using the same |
JP2002526193A (en) | 1998-09-18 | 2002-08-20 | ユナイテッド ステイツ サージカル コーポレーション | Intravascular fastener applicator |
EP1117341B1 (en) | 1998-09-30 | 2004-12-29 | Bard Peripheral Vascular, Inc. | Delivery mechanism for implantable stent |
US6203550B1 (en) | 1998-09-30 | 2001-03-20 | Medtronic, Inc. | Disposable delivery device for endoluminal prostheses |
US6273909B1 (en) | 1998-10-05 | 2001-08-14 | Teramed Inc. | Endovascular graft system |
US7563267B2 (en) | 1999-04-09 | 2009-07-21 | Evalve, Inc. | Fixation device and methods for engaging tissue |
US6287335B1 (en) | 1999-04-26 | 2001-09-11 | William J. Drasler | Intravascular folded tubular endoprosthesis |
US6146339A (en) | 1999-05-24 | 2000-11-14 | Advanced Cardiovascular Systems | Guide wire with operator controllable tip stiffness |
US6398802B1 (en) * | 1999-06-21 | 2002-06-04 | Scimed Life Systems, Inc. | Low profile delivery system for stent and graft deployment |
US6409757B1 (en) | 1999-09-15 | 2002-06-25 | Eva Corporation | Method and apparatus for supporting a graft assembly |
AU2001234948B2 (en) | 2000-02-09 | 2005-09-08 | Eva Corporation | Surgical fastener |
US6607555B2 (en) | 2000-02-15 | 2003-08-19 | Eva Corporation | Delivery catheter assembly and method of securing a surgical component to a vessel during a surgical procedure |
US6730119B1 (en) | 2000-10-06 | 2004-05-04 | Board Of Regents Of The University Of Texas System | Percutaneous implantation of partially covered stents in aneurysmally dilated arterial segments with subsequent embolization and obliteration of the aneurysm cavity |
JP3506676B2 (en) | 2001-01-25 | 2004-03-15 | Necエレクトロニクス株式会社 | Semiconductor device |
US6761733B2 (en) * | 2001-04-11 | 2004-07-13 | Trivascular, Inc. | Delivery system and method for bifurcated endovascular graft |
US20040138734A1 (en) | 2001-04-11 | 2004-07-15 | Trivascular, Inc. | Delivery system and method for bifurcated graft |
US7637932B2 (en) | 2001-11-28 | 2009-12-29 | Aptus Endosystems, Inc. | Devices, systems, and methods for prosthesis delivery and implantation |
CA2464048C (en) | 2001-11-28 | 2010-06-15 | Lee Bolduc | Endovascular aneurysm repair system |
US20090112302A1 (en) | 2001-11-28 | 2009-04-30 | Josh Stafford | Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation |
US9320503B2 (en) | 2001-11-28 | 2016-04-26 | Medtronic Vascular, Inc. | Devices, system, and methods for guiding an operative tool into an interior body region |
US7147657B2 (en) | 2003-10-23 | 2006-12-12 | Aptus Endosystems, Inc. | Prosthesis delivery systems and methods |
US20070073389A1 (en) | 2001-11-28 | 2007-03-29 | Aptus Endosystems, Inc. | Endovascular aneurysm devices, systems, and methods |
WO2003079935A1 (en) * | 2002-03-18 | 2003-10-02 | Eva Corporation | Method and apparatus to attach an unsupported surgical component |
AU2003273575B2 (en) * | 2002-05-29 | 2007-12-06 | Cook Incorporated | Trigger wire system for a prosthesis deployment device |
US7264632B2 (en) * | 2002-06-07 | 2007-09-04 | Medtronic Vascular, Inc. | Controlled deployment delivery system |
US7611528B2 (en) * | 2003-01-24 | 2009-11-03 | Medtronic Vascular, Inc. | Stent-graft delivery system |
EP1682045A2 (en) | 2003-10-23 | 2006-07-26 | Peacock, James C., III | Stent-graft assembly formed in-situ |
US7306623B2 (en) | 2005-01-13 | 2007-12-11 | Medtronic Vascular, Inc. | Branch vessel graft design and deployment method |
-
2003
- 2003-10-23 US US10/692,283 patent/US7147657B2/en not_active Expired - Lifetime
-
2004
- 2004-08-25 ES ES04782144T patent/ES2356352T3/en active Active
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- 2004-08-25 DE DE602004022446T patent/DE602004022446D1/en active Active
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- 2004-08-25 EP EP04782144A patent/EP1682039B1/en not_active Not-in-force
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- 2004-08-25 DK DK04782144T patent/DK1682039T3/en active
- 2004-08-25 CA CA002539265A patent/CA2539265A1/en not_active Abandoned
- 2004-08-25 AT AT04782144T patent/ATE438362T1/en not_active IP Right Cessation
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-
2010
- 2010-06-18 JP JP2010139939A patent/JP2010227613A/en active Pending
-
2011
- 2011-11-08 US US13/291,942 patent/US20120059450A1/en not_active Abandoned
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9320591B2 (en) | 2001-11-28 | 2016-04-26 | Medtronic Vascular, Inc. | Devices, systems, and methods for prosthesis delivery and implantation, including the use of a fastener tool |
US10098770B2 (en) | 2001-11-28 | 2018-10-16 | Medtronic Vascular, Inc. | Endovascular aneurysm devices, systems, and methods |
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DK1682039T3 (en) | 2009-11-02 |
ES2356352T3 (en) | 2011-04-07 |
DE602004022446D1 (en) | 2009-09-17 |
WO2005044073A2 (en) | 2005-05-19 |
CN1870950B (en) | 2010-05-26 |
ATE438362T1 (en) | 2009-08-15 |
WO2005044073A3 (en) | 2006-03-09 |
AU2004287353A1 (en) | 2005-05-19 |
JP4912883B2 (en) | 2012-04-11 |
CA2539265A1 (en) | 2005-05-19 |
JP2007508893A (en) | 2007-04-12 |
US20050090834A1 (en) | 2005-04-28 |
US8080050B2 (en) | 2011-12-20 |
EP1682039A2 (en) | 2006-07-26 |
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